EP3664748A1 - Herzklappenprothese mit segelkonnektoren - Google Patents
Herzklappenprothese mit segelkonnektorenInfo
- Publication number
- EP3664748A1 EP3664748A1 EP18752635.5A EP18752635A EP3664748A1 EP 3664748 A1 EP3664748 A1 EP 3664748A1 EP 18752635 A EP18752635 A EP 18752635A EP 3664748 A1 EP3664748 A1 EP 3664748A1
- Authority
- EP
- European Patent Office
- Prior art keywords
- tab
- leaflet
- fold
- stitching
- panel
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Pending
Links
- 238000011144 upstream manufacturing Methods 0.000 claims description 181
- 238000000034 method Methods 0.000 claims description 56
- 239000012530 fluid Substances 0.000 claims description 24
- 239000004744 fabric Substances 0.000 claims description 16
- 230000004044 response Effects 0.000 claims description 16
- 239000000853 adhesive Substances 0.000 claims description 10
- 230000001070 adhesive effect Effects 0.000 claims description 10
- 238000005452 bending Methods 0.000 claims description 2
- 239000007943 implant Substances 0.000 description 157
- 230000008878 coupling Effects 0.000 description 107
- 238000010168 coupling process Methods 0.000 description 107
- 238000005859 coupling reaction Methods 0.000 description 107
- 210000004027 cell Anatomy 0.000 description 23
- 210000001519 tissue Anatomy 0.000 description 22
- 230000000712 assembly Effects 0.000 description 15
- 238000000429 assembly Methods 0.000 description 15
- 239000002775 capsule Substances 0.000 description 11
- 210000003709 heart valve Anatomy 0.000 description 10
- 238000002513 implantation Methods 0.000 description 10
- 239000008280 blood Substances 0.000 description 8
- 210000004369 blood Anatomy 0.000 description 8
- 230000002861 ventricular Effects 0.000 description 8
- 230000006835 compression Effects 0.000 description 6
- 238000007906 compression Methods 0.000 description 6
- 210000002837 heart atrium Anatomy 0.000 description 6
- HLXZNVUGXRDIFK-UHFFFAOYSA-N nickel titanium Chemical compound [Ti].[Ti].[Ti].[Ti].[Ti].[Ti].[Ti].[Ti].[Ti].[Ti].[Ti].[Ni].[Ni].[Ni].[Ni].[Ni].[Ni].[Ni].[Ni].[Ni].[Ni].[Ni].[Ni].[Ni].[Ni] HLXZNVUGXRDIFK-UHFFFAOYSA-N 0.000 description 6
- 229910001000 nickel titanium Inorganic materials 0.000 description 6
- 238000004873 anchoring Methods 0.000 description 5
- 230000007704 transition Effects 0.000 description 5
- 210000003850 cellular structure Anatomy 0.000 description 4
- 230000017531 blood circulation Effects 0.000 description 3
- 238000005520 cutting process Methods 0.000 description 3
- 210000005003 heart tissue Anatomy 0.000 description 3
- 230000002401 inhibitory effect Effects 0.000 description 3
- 239000000463 material Substances 0.000 description 3
- 206010067171 Regurgitation Diseases 0.000 description 2
- 238000004026 adhesive bonding Methods 0.000 description 2
- 210000003484 anatomy Anatomy 0.000 description 2
- 238000013459 approach Methods 0.000 description 2
- 230000001174 ascending effect Effects 0.000 description 2
- 230000001746 atrial effect Effects 0.000 description 2
- 230000008901 benefit Effects 0.000 description 2
- 238000002788 crimping Methods 0.000 description 2
- 229910003460 diamond Inorganic materials 0.000 description 2
- 239000010432 diamond Substances 0.000 description 2
- 238000004519 manufacturing process Methods 0.000 description 2
- 210000004115 mitral valve Anatomy 0.000 description 2
- 208000031225 myocardial ischemia Diseases 0.000 description 2
- 210000003540 papillary muscle Anatomy 0.000 description 2
- 230000009467 reduction Effects 0.000 description 2
- 238000005476 soldering Methods 0.000 description 2
- 238000003466 welding Methods 0.000 description 2
- 238000010146 3D printing Methods 0.000 description 1
- 241001581440 Astroides Species 0.000 description 1
- 102000008186 Collagen Human genes 0.000 description 1
- 108010035532 Collagen Proteins 0.000 description 1
- 208000036829 Device dislocation Diseases 0.000 description 1
- 206010016803 Fluid overload Diseases 0.000 description 1
- WYTGDNHDOZPMIW-RCBQFDQVSA-N alstonine Natural products C1=CC2=C3C=CC=CC3=NC2=C2N1C[C@H]1[C@H](C)OC=C(C(=O)OC)[C@H]1C2 WYTGDNHDOZPMIW-RCBQFDQVSA-N 0.000 description 1
- 210000001765 aortic valve Anatomy 0.000 description 1
- 238000010009 beating Methods 0.000 description 1
- 230000000747 cardiac effect Effects 0.000 description 1
- 230000008859 change Effects 0.000 description 1
- 229920001436 collagen Polymers 0.000 description 1
- 230000007423 decrease Effects 0.000 description 1
- 230000003247 decreasing effect Effects 0.000 description 1
- 230000001419 dependent effect Effects 0.000 description 1
- 230000010339 dilation Effects 0.000 description 1
- 238000006073 displacement reaction Methods 0.000 description 1
- 230000004064 dysfunction Effects 0.000 description 1
- 238000003384 imaging method Methods 0.000 description 1
- 230000005764 inhibitory process Effects 0.000 description 1
- 230000000302 ischemic effect Effects 0.000 description 1
- 238000003698 laser cutting Methods 0.000 description 1
- 210000005246 left atrium Anatomy 0.000 description 1
- 210000005240 left ventricle Anatomy 0.000 description 1
- 239000007788 liquid Substances 0.000 description 1
- 238000012423 maintenance Methods 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 229920000728 polyester Polymers 0.000 description 1
- 229920000642 polymer Polymers 0.000 description 1
- 238000003825 pressing Methods 0.000 description 1
- 230000002441 reversible effect Effects 0.000 description 1
- 238000007789 sealing Methods 0.000 description 1
- 238000004904 shortening Methods 0.000 description 1
- 210000003291 sinus of valsalva Anatomy 0.000 description 1
- 230000008467 tissue growth Effects 0.000 description 1
- 238000012876 topography Methods 0.000 description 1
- 210000000591 tricuspid valve Anatomy 0.000 description 1
- 230000003313 weakening effect Effects 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
- A61F2/2412—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body with soft flexible valve members, e.g. tissue valves shaped like natural valves
- A61F2/2418—Scaffolds therefor, e.g. support stents
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
- A61F2/2412—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body with soft flexible valve members, e.g. tissue valves shaped like natural valves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
- A61F2/2412—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body with soft flexible valve members, e.g. tissue valves shaped like natural valves
- A61F2/2415—Manufacturing methods
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23P—METAL-WORKING NOT OTHERWISE PROVIDED FOR; COMBINED OPERATIONS; UNIVERSAL MACHINE TOOLS
- B23P15/00—Making specific metal objects by operations not covered by a single other subclass or a group in this subclass
- B23P15/001—Making specific metal objects by operations not covered by a single other subclass or a group in this subclass valves or valve housings
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
- A61F2/2427—Devices for manipulating or deploying heart valves during implantation
- A61F2/2436—Deployment by retracting a sheath
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2210/00—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2210/0014—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2220/0025—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2220/0025—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
- A61F2220/0075—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements sutured, ligatured or stitched, retained or tied with a rope, string, thread, wire or cable
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0063—Three-dimensional shapes
- A61F2230/0069—Three-dimensional shapes cylindrical
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0063—Three-dimensional shapes
- A61F2230/0093—Umbrella-shaped, e.g. mushroom-shaped
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2240/00—Manufacturing or designing of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2240/001—Designing or manufacturing processes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0014—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
- A61F2250/0039—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in diameter
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0058—Additional features; Implant or prostheses properties not otherwise provided for
- A61F2250/006—Additional features; Implant or prostheses properties not otherwise provided for modular
- A61F2250/0063—Nested prosthetic parts
Definitions
- the present application is related to:
- Some applications of the present invention relate in general to valve replacement. More specifically, some applications of the present invention relate to prosthetic valves for replacement of a cardiac valve.
- Ischemic heart disease causes regurgitation of a heart valve by the combination of ischemic dysfunction of the papillary muscles, and the dilatation of the ventricle that is present in ischemic heart disease, with the subsequent displacement of the papillary muscles and the dilatation of the valve annulus. Dilation of the annulus of the valve prevents the valve leaflets from fully coapting when the valve is closed. Regurgitation of blood from the ventricle into the atrium results in increased total stroke volume and decreased cardiac output, and ultimate weakening of the ventricle secondary to a volume overload and a pressure overload of the atrium.
- an implant having a tubular portion, an upstream support portion and one or more flanges.
- the implant is assembled from two concentric frames.
- An inner frame defines the tubular portion and the upstream support portion, and an outer frame defines the flanges.
- the implant is percutaneously deliverable to a native heart valve in a compressed state, and is expandable at the native valve.
- the implant is secured at a native heart valve by sandwiching tissue of the native valve between the upstream support portion and the flanges.
- the outer frame is radially thicker than the inner frame.
- the outer frame is undersized with respect to the inner frame, such that it constrains the inner frame even in a relaxed expanded state of the implant, and such that even in the relaxed expanded state residual stress is present in one or both of the frames.
- a toroidal space is defined by the tubular portion, the upstream support portion, and the flanges.
- the implant is configured such that the toroidal space is dimensioned proportionally to dimensions of the tubular portion.
- prosthetic leaflets are secured within a prosthetic valve via connectors, each connector comprising a unitary flexible sheet folded to define a panel, and leaflet-engaging tabs between which commissural portions of the prosthetic leaflets are secured.
- the unitary flexible sheet is folded to also define other features, such as flaps that facilitate coupling of the connector to the frame of the prosthetic valve.
- a method for use with a flexible sheet that, in an unfolded state of the sheet, defines a panel at a medial region of the sheet, a first tab portion disposed peripherally to the panel, and a second tab portion disposed peripherally to the panel opposite the first tab portion, the method including:
- first tab portion sandwiching, between the first tab portion and the second tab portion, (i) a first commissural portion of a first prosthetic leaflet, and (ii) a second commissural portion of a second prosthetic leaflet;
- first tab portion and the second tab portion attaching the first tab portion and the second tab portion to the flexible sheet by stitching a first stitching through the first tab -portion, the first commissural portion, the second commissural portion, and the second tab-portion;
- first tab portion back against itself to form the first tab portion into a first tab having first-tab outer layer and a first-tab inner layer, such that the first-tab inner layer is sandwiched between the first-tab outer layer and the first commissural portion, and
- the step of sandwiching includes sandwiching a separate flexible sheet between the first commissural portion and the second commissural portion.
- stitching the first stitching includes stitching the first stitching through (i) the first tab-portion, (ii) the first commissural portion, (iii) a separate flexible sheet disposed between the first commissural portion and the second commissural portion, (iv) the second commissural portion, and (v) the second tab-portion.
- the step of sandwiching includes sandwiching a fabric divider between the first tab portion and the second tab portion.
- the step of sandwiching includes sandwiching a separate flexible sheet between the first commissural portion and the second commissural portion, and stitching the first stitching includes stitching the first stitching through the separate flexible sheet.
- stitching the second stitching includes stitching the second stitching through the separate flexible sheet.
- the flexible sheet is a first flexible sheet
- the steps of sandwiching, attaching, covering, and stitching the second stitching are steps in assembling the first flexible sheet into a first commissure at which the first prosthetic leaflet and the second prosthetic leaflet meet, and the method further includes:
- assembling a valvular assembly that includes the first commissure, a second commissure, a third commissure, the first prosthetic leaflet, the second prosthetic leaflet, and a third prosthetic leaflet, by:
- first, second, and third prosthetic leaflets are arranged within the lumen to facilitate upstream-to-downstream fluid flow through the lumen by the first, second, and third prosthetic leaflets opening, and to inhibit downstream-to-upstream fluid flow through the lumen by the first, second, and third prosthetic leaflets closing, and
- the panel is disposed against an inner surface of the tubular frame, and the first tab and the second tab extend away from the panel into the lumen.
- assembling the flexible sheet into the commissure includes assembling the flexible sheet into the commissure such that the first tab and the second tab each define a loose region, radially inward from the first stitching and the second stitching, that is loose with respect to the prosthetic leaflets that meet at the commissure.
- securing the valvular assembly within the lumen includes securing the valvular assembly within the lumen such that, for each of the commissures, in response to the first, second, and third prosthetic leaflets opening, at least part of the first tab and at least part of the second tab move away from each other, and in response to the first, second, and third prosthetic leaflets closing, at least part of the first tab and at least part of the second tab move toward each other.
- the method further includes, subsequently to stitching the second stitching, securing the panel against an inner surface of a tubular frame, such that (i) the first tab, the second tab, the first prosthetic leaflet, and the second prosthetic leaflet extend away from the panel into a lumen defined by the tubular frame, and (ii) the first and second leaflets are arranged to facilitate upstream-to-downstream fluid flow through the lumen, and to inhibit downstream-to-upstream fluid flow through the lumen.
- the sheet in its unfolded state, further defines a plurality of flaps disposed peripherally to the panel, and securing the panel against the inner surface of the tubular frame includes folding each flap of the plurality of flaps around a respective component of the tubular frame.
- securing the panel against the inner surface of the tubular frame further includes stitching each flap of the plurality of flaps to the respective component of the tubular frame.
- the method further includes (i) forming a first cushion by folding a first-tab fold in a downstream edge of the first tab portion, and (ii) forming a second cushion by folding a second-tab fold in a downstream edge of the second tab portion.
- forming the first cushion and forming the second cushion include forming the first cushion and forming the second cushion such that, after the panel has been secured against the inner surface of the inner frame, the first cushion and the second cushion are disposed downstream of the first prosthetic leaflet and the second prosthetic leaflet.
- forming the first cushion and forming the second cushion include forming the first cushion and forming the second cushion such that, after the panel has been secured against the inner surface of the inner frame, neither the first cushion nor the second cushion is in contact with the first prosthetic leaflet or the second prosthetic leaflet.
- forming the first cushion includes forming the first cushion such that, after the panel has been secured against the inner surface of the inner frame, the first tab defines a downstream opening between the first-tab inner layer and the first-tab outer layer
- forming the second cushion includes forming the second cushion such that, after the panel has been secured against the inner surface of the inner frame, the second tab portion defines a downstream opening between the second-tab inner layer and the second-tab outer layer.
- forming the first cushion includes folding the first-tab fold such that, after the panel has been secured against the inner surface of the inner frame, the first-tab fold is disposed between the first-tab inner layer and the first-tab outer layer, and
- forming the second cushion includes folding the second-tab fold such that, after the panel has been secured against the inner surface of the inner frame, the second-tab fold is disposed between the second-tab inner layer and the second-tab outer layer.
- the first-tab fold is a first-tab outer fold
- the second-tab fold is a second-tab outer fold
- forming the first cushion further includes folding a first-tab inner fold in the downstream edge of the first tab portion, such that after the panel has been secured against the inner surface of the inner frame:
- the first-tab outer fold is continuous with the first-tab outer layer, and is disposed between the first-tab outer layer and the first-tab inner fold, and
- the first-tab inner fold is continuous with the first-tab inner layer, and is disposed between the first-tab inner layer and the first-tab outer fold, and forming the second cushion further includes folding a second-tab inner fold in the downstream edge of the second tab portion, such that after the panel has been secured against the inner surface of the inner frame:
- the second-tab outer fold is continuous with the second-tab outer layer, and is disposed between the second-tab outer layer and the second-tab inner fold
- the second-tab inner fold is continuous with the second-tab inner layer, and is disposed between the second-tab inner layer and the second-tab outer fold.
- forming the first-tab cushion includes forming the first-tab cushion prior to folding the first tab-portion back against itself, and forming the second-tab cushion includes forming the second-tab cushion prior to folding the second tab-portion back against itself.
- forming the first-tab cushion and forming the second-tab cushion includes forming the first-tab cushion and forming the second-tab cushion subsequently to stitching the first stitching.
- the first tab portion defines a plurality of first-tab portion suture holes arranged in: a first row,
- the second tab portion defines a plurality of second-tab portion suture holes arranged in:
- stitching the first stitching through the first tab-portion, the first commissural portion, the second commissural portion, and the second tab-portion includes stitching the first stitching through the second row, the first commissural portion, the second commissural portion, and the fifth row.
- folding the first tab portion back against itself includes folding the first tab portion along a fold line such that an angle between the fold line and the first row is substantially equal to an angle between the fold line and the third row.
- folding the first tab portion back against itself includes folding the first tab portion such that an angle between the fold line and the second row is smaller than both (i) the angle between the fold line and the first row, and (ii) the angle between the fold line and the third row.
- folding the first tab portion back against itself includes folding the first tab portion back against itself such that the first-tab outer layer covers the second row, and the third row is aligned with the first row, and
- folding the second tab portion back against itself includes folding the second tab portion back against itself such that the second-tab outer layer covers the fifth row, and the sixth row is aligned with the fourth row.
- stitching the second stitching through the first-tab outer layer, the first-tab inner layer, the first commissural portion, the second commissural portion, the second-tab inner layer, and the second-tab outer layer includes stitching the second stitching through the third row, the first row, the first commissural portion, the second commissural portion, the fourth row, and the sixth row.
- the method further includes, subsequently to stitching the second stitching, bringing the panel closer to the first prosthetic leaflet and the second prosthetic leaflet.
- bringing the panel closer includes moving an unstitched part of the first commissural portion away from an unstitched part of the second commissural portion.
- bringing the panel closer includes sandwiching unstitched parts of the first commissural portion and unstitched parts of the second commissural portion between the panel and another region of the sheet.
- bringing the panel closer to the first prosthetic leaflet and the second prosthetic leaflet includes flattening the panel.
- the step of sandwiching includes bending the panel.
- apparatus including:
- a unitary flexible sheet folded to define: a panel, defining a plane, and having a first side facing in a first direction away from the plane, and a second side that is opposite the first side;
- a first tab disposed on the first side of the panel, and protruding in the first direction away from the panel;
- a second tab disposed on the first side of the panel, and protruding in the first direction away from the panel;
- first prosthetic leaflet having a first-leaflet commissural portion disposed between the first tab and the second tab;
- a second prosthetic leaflet having a second-leaflet commissural portion disposed between the first tab and the second tab;
- the sheet is folded to define a first cushion at a downstream edge of the first tab, the first cushion being configured and positioned to inhibit deflection of a downstream portion of the first prosthetic leaflet away from the second prosthetic leaflet and toward the plane, and
- the sheet is folded to define a second cushion at a downstream edge of the second tab, the second cushion being configured and positioned to inhibit deflection of a downstream portion of the second prosthetic leaflet away from the first prosthetic leaflet and toward the plane.
- the apparatus further includes a separate flexible sheet, sandwiched between the first-leaflet commissural portion and the second-leaflet commissural portion.
- first cushion and the second cushion are disposed downstream of the first prosthetic leaflet and the second prosthetic leaflet.
- the sheet is folded such that the first tab has a first-tab outer layer and a first-tab inner layer, and the second tab has a second-tab outer layer and a second-tab inner layer,
- the first-leaflet commissural portion is disposed between the first-tab inner layer and the second-tab inner layer
- the second-leaflet commissural portion is disposed between the first-tab inner layer and the second-tab inner layer.
- the first tab defines a downstream opening between the first-tab inner layer and the first-tab outer layer
- the second tab portion defines a downstream opening between the second-tab inner layer and the second-tab outer layer.
- the sheet defines a first-tab fold and a second-tab fold
- the first cushion includes the first-tab fold, folded between the first-tab inner layer and the first-tab outer layer, and
- the second cushion includes the second-tab fold, folded between the second-tab inner layer and the second-tab outer layer.
- the first-tab fold is secured by stitching
- the second-tab fold is secured by stitching
- the first-tab fold is a first-tab outer fold, continuous with the first-tab outer layer
- the second-tab fold is a second-tab outer fold, continuous with the second-tab outer layer
- the sheet further defines:
- the first cushion includes:
- the second cushion includes:
- apparatus including:
- a unitary flexible sheet folded to define: a panel, having a first side facing in a first direction, and a second side that is opposite the first side;
- first tab disposed on the first side of the panel, having a first-tab outer layer and a first-tab inner layer, and protruding in the first direction away from the panel;
- a second tab disposed on the first side of the panel, having a second-tab outer layer and a second-tab inner layer, and protruding in the first direction away from the panel;
- first prosthetic leaflet having a first-leaflet commissural portion disposed between the first- tab inner layer and the second-tab inner layer;
- a second prosthetic leaflet having a second-leaflet commissural portion disposed between the first-tab inner layer and the second-tab inner layer;
- first-tab outer layer and the second-tab outer layer cover the first stitching.
- the apparatus further includes an adhesive disposed on at least one stitching selected from the group consisting of: the first stitching, and the second stitching.
- the sheet is folded along a first-tab fold line to define the first-tab outer layer and the first-tab inner layer, and the first-tab fold line is closer to the first stitching than to the second stitching, and
- the sheet is folded along a second-tab fold line to define the second-tab outer layer and the second-tab inner layer, and the second-tab fold line is closer to the first stitching than to the second stitching.
- the sheet is folded along a first-tab fold line to define the first-tab outer layer and the first-tab inner layer, and an angle between the first-tab fold line and the first stitching is smaller than an angle between the first-tab fold line and the second stitching, and the sheet is folded along a second-tab fold line to define the second-tab outer layer and the second-tab inner layer, and an angle between the second-tab fold line and the first stitching is smaller than an angle between the second-tab fold line and the second stitching.
- the apparatus further includes a separate flexible sheet, sandwiched between the first-leaflet commissural portion and the second-leaflet commissural portion.
- the apparatus further includes a tubular frame that defines a lumen, and:
- the panel is disposed against an inner surface of the tubular frame
- first prosthetic leaflet and the second prosthetic leaflet are secured within the lumen by the flexible sheet being connected to the tubular frame.
- the apparatus further includes a separate flexible sheet, disposed between the first-leaflet commissural portion and the second-leaflet commissural portion, the first stitching being stitched through the separate flexible sheet.
- the second stitching is stitched through the separate flexible sheet.
- the flexible sheet is a first flexible sheet
- the first-leaflet commissural portion is a first first-leaflet commissural portion
- the second-leaflet commissural portion is a first second-leaflet commissural portion
- first flexible sheet, the first first-leaflet commissural portion, and the first second - leaflet commissural portion are arranged to collectively define a first commissure
- the first leaflet has a second first-leaflet commissural portion
- the second leaflet has a second second-leaflet commissural portion
- the apparatus further includes:
- a third prosthetic leaflet having a first third-leaflet commissural portion and a second third-leaflet commissural portion
- the second second-leaflet commissural portion, the first third-leaflet commissural portion, and the second flexible sheet are arranged to collectively define a second commissure, the second first-leaflet commissural portion, the second third-leaflet commissural portion, and the third flexible sheet are arranged to collectively define a third commissure, the first commissure, the second commissure, the third commissure, the first leaflet, the second leaflet, and the third leaflet, are arranged to define a valvular assembly that is secured within the lumen by the first flexible sheet, the second flexible sheet, and the third flexible sheet being connected to the tubular frame, and
- the valvular assembly is configured to facilitate upstream-to-downstream fluid flow through the lumen by the first, second, and third prosthetic leaflets opening, and to inhibit downstream-to-upstream fluid flow through the lumen by the first, second, and third prosthetic leaflets closing.
- the first tab and the second tab each defines a loose region, radially inward from the first stitching and the second stitching, that is loose with respect to the prosthetic leaflets that meet at the commissure.
- the valvular assembly is configured such that, for each of the commissures, in response to the first, second, and third prosthetic leaflets opening, at least part of the first tab and at least part of the second tab move away from each other, and in response to the first, second, and third prosthetic leaflets closing, at least part of the first tab and at least part of the second tab move toward each other.
- the apparatus further includes a tubular frame that is shaped to define a lumen, and the panel is secured against an inner surface of a tubular frame, such that (i) the first tab, the second tab, the first prosthetic leaflet, and the second prosthetic leaflet extend away from the panel into the lumen, and (ii) the first and second leaflets are arranged to facilitate upstream-to-downstream fluid flow through the lumen, and to inhibit downstream-to-upstream fluid flow through the lumen.
- the sheet defines a plurality of flaps extending from the panel, and the panel is secured against the inner surface of the tubular frame by each flap of the plurality of flaps being folded around a respective component of the tubular frame.
- each flap of the plurality of flaps is stitched to the respective component of the tubular frame.
- the sheet is folded to define a first cushion at a downstream edge of the first tab, and a second cushion at a downstream edge of the second tab.
- the first cushion and the second cushion are disposed downstream of the first prosthetic leaflet and the second prosthetic leaflet.
- neither the first cushion nor the second cushion is in contact with the first prosthetic leaflet or the second prosthetic leaflet.
- the first tab defines a downstream opening between the first-tab inner layer and the first-tab outer layer
- the second tab portion defines a downstream opening between the second-tab inner layer and the second-tab outer layer.
- the sheet defines a first-tab fold and a second-tab fold
- the first cushion includes the first-tab fold, folded between the first-tab inner layer and the first-tab outer layer, and
- the second cushion includes the second-tab fold, folded between the second-tab inner layer and the second-tab outer layer.
- the first-tab fold is a first-tab outer fold, continuous with the first-tab outer layer
- the second-tab fold is a second-tab outer fold, continuous with the second-tab outer layer
- the sheet further defines:
- the first cushion includes:
- the second cushion includes:
- the first stitching is stitched along a first stitch line
- the second stitching is stitched along a second stitch line
- the first stitch line and the second stitch line diverge from each other at 10-45 degrees.
- first stitch line and the second stitch line diverge from each other at 10-30 degrees. In an application, the first stitch line and the second stitch line diverge from each other at 15-25 degrees.
- the first stitch line and the second stitch line diverge from each other at 20 degrees.
- apparatus for use with a prosthetic valve including a connector, the connector including a flexible sheet that is folded to define:
- a panel having a first side facing in a first direction, and a second side that is opposite the first side;
- a leaflet receptacle disposed on the first side of the panel, and protruding in the first direction away from the panel;
- each flap folded about a respective fold axis such that at least part of each flap is disposed on the second side of the panel.
- the panel has an edge between the first side and the second side, and each flap is foldable over the edge, so as to be disposed on the second side of the panel.
- the plurality of flaps is arranged in a circuit such that each flap has two adjacent flaps around the circuit, and the fold axis of each flap is oriented at 60-120 degrees from the fold axis of each of its adjacent flaps.
- the flexible sheet is a single unitary flexible sheet, and the unitary flexible sheet is folded to define the panel, the leaflet receptacle, and the plurality of flaps.
- the plurality of flaps includes exactly four flaps.
- the leaflet receptacle includes:
- first leaflet-engaging tab extending from the first side of the panel, and defining a first row of first-tab stitching holes and a second row of first-tab stitching holes
- second leaflet-engaging tab extending from the first side of the panel, and defining a first row of second-tab stitching holes and a second row of second-tab stitching holes
- the receptacle is configured to sandwich one or more prosthetic valve leaflets between the leaflet-engaging tabs such that, on opposite sides of the sandwiched leaflets:
- first row of first-tab stitching holes and the first row of second-tab stitching holes are aligned with each other, and
- the second row of first-tab stitching holes and the second row of second-tab stitching holes are aligned with each other.
- the first row of first- tab stitching holes and the second row of first- tab stitching holes diverge at 10-45 degrees from each other, and the first row of second-tab stitching holes and the second row of second-tab stitching holes diverge at 10-45 degrees from each other.
- first row of first-tab stitching holes and the second row of first- tab stitching holes diverge at 10-30 degrees from each other, and the first row of second-tab stitching holes and the second row of second-tab stitching holes diverge at 10-30 degrees from each other.
- first row of first-tab stitching holes and the second row of first- tab stitching holes diverge at 15-25 degrees from each other, and the first row of second-tab stitching holes and the second row of second-tab stitching holes diverge at 15-25 degrees from each other.
- each of the first leaflet- engaging tab and the second leaflet-engaging tab includes (i) an outer layer, and (ii) an inner layer that is positioned to be sandwiched between the outer layer and the one or more leaflets, and:
- first and second rows of first-tab stitching holes are defined in the inner layer of the first leaflet-engaging tab
- the first and second rows of second-tab stitching holes are defined in the inner layer of the second leaflet-engaging tab.
- the first leaflet-engaging tab further defines a third row of first-tab stitching holes, defined in the outer layer of the first leaflet-engaging tab, and aligned with the first row of first-tab stitching holes,
- the second leaflet-engaging tab further defines a third row of second-tab stitching holes, defined in the outer layer of the second leaflet-engaging tab, and aligned with the first row of second-tab stitching holes.
- the apparatus further includes:
- first prosthetic leaflet and a second prosthetic leaflet, the first and second prosthetic leaflets disposed within the lumen
- the apparatus defines a commissure at which the first and second leaflets meet each other and are coupled to the frame via the connector.
- the leaflets define an upstream end and a downstream end of the lumen by being arranged and coupled to the frame so as to facilitate one-way fluid flow through the lumen.
- the leaflet receptacle includes:
- first leaflet-engaging tab extending from the first side of the panel
- second leaflet-engaging tab extending from the first side of the panel
- first and second leaflets are sandwiched together between the first and second leaflet-engaging tabs, and are stitched to the first and second leaflet-engaging tabs such that, on opposite sides of the sandwiched leaflets:
- first row of first-tab stitching holes and the first row of second-tab stitching holes are aligned with each other, and
- the second row of first-tab stitching holes and the second row of second-tab stitching holes are aligned with each other.
- the first leaflet has a first-leaflet downstream edge
- the second leaflet has a second-leaflet downstream edge
- each of the first and second leaflet- engaging tabs extends in a downstream direction beyond the first-leaflet downstream edge and the second-leaflet downstream edge.
- the first leaflet has a first-leaflet downstream edge
- the second leaflet has a second-leaflet downstream edge
- the first and second leaflets are configured:
- first and second leaflets moving away from each other in response to the fluid flow in a downstream direction, such that the first-leaflet downstream edge and the second-leaflet downstream edge move toward the frame
- the first leaflet-engaging tab defines a first cushion that inhibits movement of a commissural portion of the first leaflet toward the frame
- the second leaflet-engaging tab defines a second cushion that inhibits movement of a commissural portion of the second leaflet toward the frame.
- first cushion and the second cushion are disposed further downstream than the first- leaflet downstream edge and the second-leaflet downstream edge.
- the first and second cushions are each defined by folds in the flexible sheet.
- the leaflet receptacle includes:
- first leaflet-engaging tab extending from the first side of the panel, and defining a first row of first-tab stitching holes and a second row of first-tab stitching holes
- a second leaflet-engaging tab extending from the first side of the panel, and defining a first row of second-tab stitching holes and a second row of second-tab stitching holes;
- first and second leaflets are sandwiched together between the first and second leaflet-engaging tabs, and are stitched to the first and second leaflet-engaging tabs such that, on opposite sides of the sandwiched leaflets:
- first row of first-tab stitching holes and the first row of second-tab stitching holes are aligned with each other, and the second row of first-tab stitching holes and the second row of second-tab stitching holes are aligned with each other.
- first and second rows of first-tab stitching holes diverge from each other such that progressively downstream parts of the first and second rows of first-tab stitching holes are progressively further from each other, and the first and second rows of second-tab stitching holes diverge from each other such that progressively downstream parts of the first and second rows of second-tab stitching holes are progressively further from each other.
- first and second rows of first- tab stitching holes diverge at 10- 45 degrees from each other, and the first and second rows of second-tab stitching holes diverge at 10-45 degrees from each other.
- the connector is a first connector
- the commissure is a first commissure
- the apparatus further includes a second connector, a third connector, and a third leaflet, and
- the apparatus defines:
- the fold axis of each flap is oriented at 70-110 degrees from the fold axis of each of its adjacent flaps.
- the fold axis of each flap is oriented at 80-100 degrees from the fold axis of each of its adjacent flaps.
- the connector has a folded state in which the sheet is folded to define the panel, the leaflet receptacle, and the plurality of flaps, and the sheet further has an unfolded state in which the sheet defines a plane, and further defines, in the plane:
- the flaps disposed peripherally to the panel
- each of the tab portions disposed peripherally from the panel, and in the folded state, each of the tab portions defines a respective leaflet-engaging tab, and the leaflet receptacle includes the leaflet-engaging tab of each of the tab portions.
- a first flap part of each of the flaps is disposed on the first side of the panel, and each of the flaps is folded around the panel such that a second flap part of each of the flaps is disposed on the second side of the panel.
- the sheet further defines a first bridging element via which the first tab portion is connected to the panel, and a second bridging element via which the second tab portion is connected to the panel.
- the first and second bridging elements extend from respective edges of the panel and toward each other across the first side of the panel, and each of the first and second tab portions protrudes from the respective bridging element in the first direction away from the first side of the panel.
- the flaps are connected to the panel independently of the bridging elements. In an application, the flaps are connected to the panel via the bridging elements.
- the panel, the first and second bridging elements, and the first and second tab portions are arranged in a row that defines a lateral axis in the plane, the lateral axis passing through the panel, the first and second bridging elements, and the first and second tab portions, and for each of the bridging elements, a first flap of the plurality of flaps and a second flap of the plurality of flaps are connected to the bridging element, the lateral axis passing between the first and second flaps.
- the bridging elements are disposed on the first side of the panel, and each flap extends from one of the bridging elements and around the panel such that a flap part of each flap is disposed on the second side of the panel.
- the first tab portion and the second tab portion flank the panel by being disposed, in the plane, on opposing lateral sides of the panel.
- the first and second tab portions, the first and second bridging elements, and the panel are arranged in a row that defines a lateral axis in the plane, and the fold axis of each of the flaps is at 30-60 degrees from the lateral axis.
- a panel having a first side that faces in a first direction, and a second side that faces in a second, opposite direction;
- each flap extending from the panel, and configured to fold, over a respective fold axis, toward the second direction, the plurality of flaps arranged in a circuit such that each flap has two adjacent flaps around the circuit,
- each flap is oriented at 60-120 degrees from the fold axis of each of its adjacent flaps.
- the panel substantially defines a plane, and each flap is configured to fold, over its respective fold axis, out of the plane.
- each flap is configured to fold over a respective portion of the second side of the panel.
- the connector consists of a single unitary sheet of a material that is folded to define the panel, the leaflet-engaging tab, and the plurality of flaps.
- the plurality of flaps includes exactly four flaps.
- the fold axis of each flap is oriented at 70-110 degrees from the fold axes of its adjacent flaps.
- the fold axis of each flap is oriented at 80-100 degrees from the fold axes of its adjacent flaps.
- the fold axis of each flap is oriented at approximately 90 degrees from the fold axes of its adjacent flaps.
- a panel having a first side facing in a first direction, and a second side that is opposite the first side; a leaflet receptacle, disposed on the first side of the panel, and protruding in the first direction away from the panel; and
- each flap folded about a respective fold axis such that at least part of each flap is disposed on the second side of the panel;
- apparatus for use at a heart valve of a subject including:
- a frame assembly transluminally advanceable to the heart, and including:
- an outer stent frame that defines a ring that is coupled to the inner stent frame, and circumscribes the tubular portion
- the inner stent frame is cut from a first tube of nitinol that has a first-tube wall thickness
- the outer stent frame is cut from a second tube of nitinol that has a second-tube wall thickness that is greater than the first-tube wall thickness.
- the first-tube wall thickness is 0.45-0.65 mm
- the second-tube wall thickness is 0.6-0.8 mm.
- the second-tube wall thickness is at least 20 percent greater than the first-tube wall thickness.
- the second-tube wall thickness is at least 30 percent greater than the first-tube wall thickness.
- the inner frame further defines an annular upstream support portion, extending from the tubular portion, and dimensioned to be placed against an upstream surface of the heart valve, and
- the outer frame further defines a plurality of flanges that extend from the tubular portion, and are dimensioned to be placed against a downstream surface of the heart valve.
- an outer stent frame that:
- the inner stent frame and the outer stent frame define at least part of a frame assembly in which the outer- frame coupling elements are fixed to the inner-frame coupling elements and the ring circumscribes the tubular portion, and
- tubular portion is expandable into an expanded state in which the tubular portion defines an inner-stent-frame constrained expanded diameter that is smaller than the inner-stent- frame relaxed expanded diameter.
- the outer frame is coupled to the inner frame such that:
- the outer frame in the compressed state of the frame assembly, the outer frame is in circumferential contact with the tubular portion, and
- the outer-frame coupling elements are welded to the inner-frame coupling elements.
- the apparatus defines a plurality of commissures at which the leaflets are secured to the frame assembly
- the outer frame is secured to the inner frame by both (i) the fixation of the outer- frame coupling elements to the inner-frame coupling elements, and (ii) stitching of the outer frame to the inner frame at the commissures.
- the apparatus defines a plurality of commissures
- the apparatus includes a plurality of stitches, and commissural portions of the two prosthetic leaflets are secured to the inner stent frame and to the outer stent frame via the plurality of stitches.
- the apparatus at each commissure the apparatus includes a fabric connector to which the commissural portions of the two leaflets are secured, and the plurality of stitches secures the commissural portions of the two leaflets to the inner stent frame and the outer stent frame by being attached to the fabric connector.
- the fabric connector is shaped to define (i) a panel having a first side and a second side, (ii) one or more leaflet-engaging tabs to which the commissural portions of the two leaflets are stitched, the tabs protruding from the first side of the panel, and (iii) a plurality of flaps, wrapped around elements of the inner stent frame and elements of the outer stent frame, and secured thus by stitching.
- apparatus for use in a heart of a subject including:
- a frame assembly defining:
- a plurality of prosthetic valve leaflets coupled to the tubular portion, and disposed within the lumen
- the upstream support portion extends radially outward from the tubular portion
- the flanges extend radially outward from the tubular portion and toward the upstream support portion
- the tubular portion has a transverse cross- sectional area
- the frame assembly defines a toroidal space between the flanges, the upstream support portion, and the tubular portion, the toroidal space circumscribing the tubular portion and having a cross-sectional area that is 5- 10 percent of the transverse cross-sectional area of the tubular portion.
- the frame assembly is a first frame assembly
- the plurality of leaflets is a first plurality of leaflets
- the apparatus includes a first implant that includes the first frame assembly and the first plurality of leaflets
- the apparatus further includes a second implant that includes:
- a second frame assembly defining:
- a second upstream support portion coupled to the second tubular portion
- a second plurality of prosthetic valve leaflets coupled to the second tubular portion, and disposed within the second lumen
- the second upstream support portion extends radially outward from the second tubular portion
- the flanges of the second plurality of flanges extend radially outward from the second tubular portion and toward the second upstream support portion
- the second tubular portion has a transverse cross- sectional area that is at least 30 percent greater than the transverse cross- sectional area of the first tubular portion of the first implant
- the second frame assembly defines a second toroidal space between the flanges of the second plurality of flanges, the second upstream support portion, and the second tubular portion, the second toroidal space circumscribing the second tubular portion and having a cross-sectional area that is 5-10 percent of the transverse cross- sectional area of the second tubular portion.
- the frame assembly is dimensioned such that the cross-sectional area of the toroidal space is 5-8 percent of the transverse cross- sectional area of the tubular portion.
- the frame assembly is dimensioned such that the cross-sectional area of the toroidal space is 6-7 percent of the transverse cross- sectional area of the tubular portion.
- the frame assembly is dimensioned such that the cross-sectional area of the toroidal space is 6.5-7.5 percent of the transverse cross-sectional area of the tubular portion.
- the upstream support portion includes a plurality of arms that, in the expanded state of the frame assembly, protrude radially outward from the tubular portion.
- the tubular portion has an upstream end and a downstream end
- the prosthetic leaflets are configured to provide one-way blood flow through the lumen from the upstream end to the downstream end,
- each arm of the plurality of arms is attached to the tubular portion at a site that is downstream of the upstream end
- each arm progressively lateral portions of each arm define, respectively:
- the frame assembly defines the toroidal space between the flanges, the tubular portion, and the arch portions of the arms of the upstream support portion.
- each flange extends radially outward from the tubular portion and toward a tip of the flange, and the arch portion of the arms curves in a downstream direction past the tips of the flanges.
- apparatus for use at a heart valve of a subject including:
- each implant being transluminally advanceable to the heart, and including:
- a frame assembly that includes:
- an inner stent frame that defines a tubular portion that defines a lumen
- an outer stent frame that defines a ring that is coupled to the inner stent frame, and circumscribes the tubular portion
- a delivery tool including a delivery capsule that has a capsule diameter
- the first implant has:
- the second implant has:
- the second implant has a compressed diameter that is no more than 2 percent greater than the compressed diameter of the first implant, and is dimensioned to be housed within the delivery capsule.
- apparatus including:
- a unitary flexible sheet that, in an unfolded state of the sheet, defines:
- a panel portion at a medial region of the sheet, a first tab portion disposed peripherally to the panel, and having (i) a first part, and (ii) a second part that is disposed peripherally to the first part of the first tab portion, and
- a second tab portion disposed peripherally to the panel opposite the first tab portion, and having (i) a first part, and (ii) a second part that is disposed peripherally to the first part of the second tab portion,
- the sheet being folded into a folded state in which the sheet defines:
- a panel defined by the panel portion, having a first side facing in a first direction, and a second side that is opposite the first side;
- first tab portion defined by the first tab portion, the first tab being disposed on the first side of the panel, and having:
- first-tab inner layer defined by the first part of the first tab portion extending away from the panel in the first direction
- a second-tab outer layer defined by the second part of the first tab portion being folded back over the first part of the first tab portion, and extending back toward the panel;
- a second tab defined by the second tab portion, the second tab being disposed on the first side of the panel, and having:
- first prosthetic leaflet having a first-leaflet commissural portion sandwiched between the first-tab inner layer and the second-tab inner layer;
- a second prosthetic leaflet having a second-leaflet commissural portion sandwiched between the first-tab inner layer and the second-tab inner layer.
- the apparatus further includes a stitching, stitched through the first- tab inner layer, the first-leaflet commissural portion, the second-leaflet commissural portion, and the second-tab inner layer.
- the first-tab outer layer and the second-tab outer layer cover the stitching.
- the stitching is a first stitching
- the apparatus further includes a second stitching, stitched through the first-tab outer layer, the first-tab inner layer, the first- leaflet commissural portion, the second-leaflet commissural portion, the second-tab inner layer, and the second-tab outer layer.
- FIGs. 1A-B and 2A-E are schematic illustrations of an implant for use with a native valve of a heart of a subject, in accordance with some applications of the invention
- Figs. 3A-C are schematic illustrations that show structural changes in a frame assembly during transitioning of the assembly between its compressed and expanded states, in accordance with some applications of the invention
- FIGs. 4A-F are schematic illustrations of implantation of the implant at the native valve, in accordance with some applications of the invention.
- FIG. 5 is a schematic illustration of a step in the implantation of the implant, in accordance with some applications of the invention.
- Fig. 6 is a schematic illustration of the implant, in accordance with some applications of the invention.
- Figs. 7A-B and 8A-B are schematic illustrations of frame assemblies of respective implants, in accordance with some applications of the invention.
- FIGS. 9A-C are schematic illustrations of an implant comprising a frame assembly, in accordance with some applications of the invention.
- Fig. 10 is a schematic illustration of a frame assembly of an implant, in accordance with some applications of the invention.
- Figs. 11A-C are schematic illustrations of a connector and a commissure of a prosthetic valve, in accordance with some applications of the invention;
- Figs. 12A-B and 13A-G are schematic illustrations of a connector for connecting prosthetic leaflets to a frame of a prosthetic valve implant, in accordance with some applications of the invention.
- Figs. 14A-B are schematic illustrations of a connector for connecting prosthetic leaflets to a frame of a prosthetic valve implant, in accordance with some applications of the invention.
- Implant 20 comprises a frame assembly 22 that has an upstream end 24, a downstream end 26, and a central longitudinal axis axl therebetween.
- Frame assembly 22 comprises a valve frame 30 that comprises a tubular portion 32 that has an upstream end 34 and a downstream end 36, and is shaped to define a lumen 38 through the tubular portion from the upstream end to the downstream end.
- Tubular portion 32 circumscribes axis axl, and thereby defines lumen 38 along the axis.
- Valve frame 30 further comprises an upstream support portion 40, extending from upstream end 34 of tubular portion 32.
- Frame assembly 22 further comprises at least one leg 50, coupled to valve frame 30 at (e.g., via) a coupling point 52, and having a tissue-engaging flange 54.
- leg 50 is part of an outer frame (or “leg frame") 60, and frames 30 and 60 define respective coupling elements 31 and 61, which are fixed with respect to each other at coupling points 52.
- frames 30 and 60 are coupled to each other only at coupling points 52 (e.g., only via the fixation of coupling elements 31 and 61 with respect to each other).
- Implant 20 further comprises a valve member 58 (e.g., one or more prosthetic leaflets) disposed within lumen 38, and configured to facilitate one-way liquid flow through the lumen from upstream end 34 to downstream end 36 (e.g., thereby defining the orientation of the upstream and downstream ends of tubular portion 32).
- a valve member 58 e.g., one or more prosthetic leaflets
- Fig. 1A shows implant 20 in a fully-expanded state, in which frame assembly 22 is in a fully-expanded state.
- Fig. IB shows an exploded view of frame assembly 22 in its fully-expanded state.
- Figs. 2A-E show respective states of implant 20, which will be discussed in more detail hereinbelow with respect to the implantation of the implant and the anatomy in which the implant is implanted.
- Fig. 1A shows implant 20 in a fully-expanded state, in which frame assembly 22 is in a fully-expanded state.
- FIG. 2A shows implant 20 in a compressed state (in which frame assembly 22 is in a compressed state), for percutaneous delivery of the implant to the heart of the subject.
- leg 50 including flange 54 thereof
- upstream support portion 40 is generally tubular, collinear with tubular portion 32 (e.g., extending collinearly from the tubular portion), and disposed around axis axl.
- Fig. 2B shows a state of implant 20 in which tissue-engaging flange 54 of each leg 50 extends radially away from axis axl (e.g., radially away from tubular portion 32).
- Fig. 2C shows a state of implant 20 in which upstream-support portion 40 extends radially away from axis axl (and thereby radially away from tubular portion 32).
- Fig. 2D shows a state of implant 20 in which both flange 54 and portion 40 extend away from axis axl. In the fully- expanded state (Figs. 1A-B) both upstream support portion 40 and flange 54 extend radially away from axis axl.
- frame assembly 22 is biased (e.g., shape-set) to assume its fully-expanded state, which is shown in Fig. 2E.
- Transitioning of implant 20 between the respective states is typically controlled by delivery apparatus, such as by constraining the implant in a compressed state within a delivery tube and/or against a control rod, and selectively releasing portions of the implant to allow them to expand.
- tubular portion 32 has a diameter dl, and in the expanded state, the tubular portion has a diameter d2 that is greater that diameter dl.
- diameter dl is 4-15 mm, (e.g., 5-11 mm) and diameter d2 is 20- 50 mm, (e.g., 23-33 mm).
- tubular portion 32 bulges slightly in its middle (e.g., is slightly barrel- shaped).
- values of diameter d2 are the average diameter along the tubular portion.
- values for the cross- sectional area of the tubular portion are the average cross- sectional area along the tubular portion. This also applies to other implants described herein, mutatis mutandis.
- Frame assembly 22 is configured such that increasing the diameter of tubular portion 32 (e.g., from dl to d2) causes longitudinal movement of flange 54 away from coupling point 52. In the same way, reducing the diameter of tubular portion 32 (e.g., from d2 to dl) causes longitudinal movement of flange 54 toward coupling point 52.
- longitudinal movement means movement parallel with central longitudinal axis axl. Therefore, longitudinal movement of flange 54 away from coupling point 52 means increasing a distance, measured parallel with longitudinal axis axl, between flange 54 and coupling point 52. An example of such a configuration is described in more detail with respect to Fig. 3A.
- frame assembly 22 is configured such that increasing the diameter of tubular portion 32 also causes longitudinal movement of upstream support portion 40 toward coupling point 52, e.g., as described in more detail with respect to Figs. 3B-C.
- frame assembly 22 is configured such that increasing the diameter of tubular portion 32 also causes longitudinal movement of upstream end 34 of tubular portion 32 toward coupling point 52. In the same way, reducing the diameter of tubular portion 32 causes longitudinal movement of upstream end 34 away from coupling point 52.
- upstream support portion 40 comprises a plurality of arms 46 that each extends radially outward from tubular portion 32 (e.g., from upstream end 34 of the tubular portion). Arms 46 are typically flexible. For some such applications, arms 46 are coupled to tubular portion 32 such that each arm may deflect independently of adjacent arms during implantation (e.g., due to anatomical topography).
- upstream support portion 40 comprises a plurality of barbs 48 that extend out of a downstream surface of the upstream support portion.
- each arm 46 may comprise one or more of barbs 48.
- Barbs 48 press into tissue upstream of the native valve (e.g., into the valve annulus), thereby inhibiting downstream movement of implant 20 (in addition to inhibition of downstream movement provided by the geometry of upstream support portion 40).
- a covering 23 typically comprises a flexible sheet, such as a fabric, e.g., comprising polyester.
- covering 23 covers at least part of tubular portion 32, typically lining an inner surface of the tubular portion, and thereby defining lumen 38.
- upstream support portion 40 is covered with covering 23, e.g., extending between arms 46 to form an annular shape. It is hypothesized that this reduces a likelihood of paravalvular leakage. For such applications, excess covering 23 may be provided between arms 46 of upstream support portion 40, so as to facilitate their independent movement.
- covering 23 covering an upstream side of upstream support portion 40, the covering typically additionally (or alternatively) covers the downstream side of the upstream support portion.
- covering 23 may extend over the tips of arms 46 and down the outside of the arms, or a separate piece of covering may be provided on the downstream side of the upstream support portion.
- each arm 46 may be individually covered in a sleeve of covering 23, thereby facilitating independent movement of the arms.
- legs 50 e.g., flanges thereof
- covering 23 At least part of legs 50 (e.g., flanges thereof) is covered with covering 23.
- frame assembly 22 comprises a plurality of legs 50 (e.g., two or more legs, e.g., 2-16 legs, such as 4-12 legs, such as 6-12 legs), arranged circumferentially around valve frame 30 (e.g., around the outside of tubular portion 32).
- frame assembly 22 comprises a plurality of coupling points 52 at which the legs are coupled to valve frame 30.
- each leg 50 is typically coupled to a coupling point 52 via a strut 70.
- each leg 50 is coupled to a plurality of (e.g., two) coupling points 52 via a respective plurality of (e.g., two) struts 70.
- frame assembly 22 is arranged such that, in the expanded state of the frame assembly, leg 50 is disposed, circumferentially with respect to tubular portion 32, between two struts, and each of the two struts are disposed, circumferentially with respect to the tubular portion, between the leg and a respective coupling point 52.
- a plurality of (e.g., two) legs are coupled to each coupling point 52 via a respective plurality of (e.g., two) struts 70.
- frame assembly 22 is arranged such that, in the expanded state of the frame assembly, coupling point 52 is disposed, circumferentially with respect to tubular portion 32, between two struts 70, and each of the two struts are disposed, circumferentially with respect to the tubular portion, between the coupling point and a respective leg 50.
- frame assembly 22 comprises an outer frame (e.g., a leg frame) 60 that circumscribes tubular portion 32, comprises (or defines) the plurality of legs 50 and the plurality of struts 70, and is coupled to valve frame 30 at the plurality of coupling points 52, such that the plurality of legs are distributed circumferentially around the tubular portion.
- outer frame 60 comprises a ring 66 that is defined by a pattern of alternating peaks 64 and troughs 62, and that typically circumscribes tubular portion 32.
- the ring may comprise struts 70, extending between the peaks and troughs.
- Peaks 64 are longitudinally closer to upstream end 34 of tubular portion 32 than to downstream end 36, and troughs 62 are longitudinally closer to the downstream end than to the upstream end. (It is to be noted that throughout this patent application, including the specification and the claims, the term “longitudinally” means with respect to longitudinal axis axl.
- peaks 64 are closer than troughs 62 to upstream end 34, and troughs 62 are closer than peaks 64 to downstream end 36.
- frame 60 comprises ring 66
- each leg 50 is coupled to the ring (or defined by frame 60) at a respective trough 62.
- the peaks and troughs are defined by ring 66 having a generally zig-zag shape.
- the scope of the invention includes ring 66 having another shape that defines peaks and troughs, such as a serpentine or sinusoid shape.
- the coupling points are disposed circumferentially around the frame assembly (e.g., around axis axl), typically on a transverse plane that is orthogonal to axis axl. This transverse plane is illustrated by the position of section A-A in Fig. 2B.
- coupling points 52 may be disposed at different longitudinal heights of frame assembly 22, e.g., such that different flanges 54 are positioned and/or moved differently to others.
- coupling points 52 (and therefore coupling elements 31 and 61) are disposed longitudinally between upstream end 24 and downstream end 26 of frame assembly 22, but not at either of these ends.
- coupling points 52 are disposed longitudinally between upstream end 34 and downstream end 36 of tubular portion 32, but not at either of these ends.
- the coupling points may be more than 3 mm (e.g., 4-10 mm) both from end 34 and from end 36. It is hypothesized that this advantageously positions the coupling points at a part of tubular portion 32 that is more rigid than end 34 or end 36.
- leg 50 is typically expandable into its expanded state (e.g., a released-flange state) such that flange 54 extends away from axis axl, independently of increasing the diameter of tubular portion 32 (e.g., as shown in Figs. 2B & 2D).
- upstream support portion 40 is typically expandable into its expanded state (e.g., a released- arm state) such that it (e.g., arms 46 thereof) extends away from axis axl, independently of increasing the diameter of tubular portion 32 (e.g., as shown in Fig. 2C & 2D).
- the state shown in Fig. 2D may be considered to be an intermediate state.
- implant 20 is typically configured such that legs 50 (e.g., flanges 54 thereof) and upstream support portion 40 are expandable such that they both extend away from axis axl, while retaining a distance d3 therebetween. This distance is subsequently reducible to a distance d4 by expanding tubular portion 32 (e.g., shown in Fig. 2E).
- legs 50 e.g., flanges 54 thereof
- upstream support portion 40 are expandable such that they both extend away from axis axl, while retaining a distance d3 therebetween. This distance is subsequently reducible to a distance d4 by expanding tubular portion 32 (e.g., shown in Fig. 2E).
- flange 54 can extend away from axis axl over 40 percent (e.g., 40-80 percent, such as 40-70 percent) of the distance that it extends from the axis subsequent to the expansion of the tubular portion.
- a span dl5 of the flanges while tubular portion 32 is in its compressed state may be at least 40 percent (e.g., 40-80 percent, such as 40-70 percent) as great as a span dl6 of the flanges subsequent to the expansion of the tubular portion.
- span dl5 is greater than 15 mm and/or less than 50 mm (e.g., 20-30 mm).
- span dl6 is greater than 30 mm and/or less than 60 mm (e.g., 40-50 mm). It is to be noted that flange 54 is effectively fully expanded, with respect to other portions of leg 50 and/or with respect to tubular portion 32, before and after the expansion of the tubular portion.
- upstream support portion 40 (e.g., arms 46) can extend away from axis axl over 30 percent (e.g., 30-70 percent) of the distance that it extends from the axis subsequent to the expansion of the tubular portion. That is, for some applications, a span dl7 of the upstream support portion while tubular portion 32 is in its compressed state may be at least 30 percent (e.g., 30-70 percent) as great as a span dl8 of the upstream support portion subsequent to the expansion of the tubular portion.
- span dl7 is greater than 16 mm (e.g., greater than 20 mm) and/or less than 50 mm (e.g., 30-40 mm).
- span dl8 is greater than 40 mm and/or less than 65 mm (e.g., 45-56 mm, such as 45-50 mm). It is to be noted that upstream support portion 40 is effectively fully expanded, with respect to tubular portion 32, before and after the expansion of the tubular portion.
- flanges 54 typically translate radially outward from span dl5 to span dl6 (e.g., without deflecting).
- upstream support portion 40 behaves similarly (e.g., arms 46 translated radially outward from span dl7 to span dl8, e.g., without deflecting). That is, an orientation of each flange 54 and/or each arm 46 with respect to tubular portion 32 and/or axis axl is typically the same in the state shown in Fig. 2D as it is in the state shown in Fig. 2E. Similarly, for some applications an orientation of each flange 54 with respect to upstream support portion 40 (e.g., with respect to one or more arms 46 thereof) is the same before and after expansion of tubular portion 32.
- increasing the diameter of tubular portion 32 from dl to d2 causes greater than 1 mm and/or less than 20 mm (e.g., 1-20 mm, such as 1-10 mm or 5-20 mm) of longitudinal movement of flange 54 away from coupling point 52.
- increasing the diameter of tubular portion 32 from dl to d2 causes greater than 1 mm and/or less than 20 mm (e.g., 1-20 mm, such as 1-10 mm or 5-20 mm) of longitudinal movement of upstream support portion 40 toward coupling point 52.
- distance d3 is 7-30 mm.
- distance d4 is 0-15 mm (e.g., 2-15 mm).
- increasing the diameter of tubular portion 32 from dl to d2 reduces the distance between the upstream support portion and flanges 54 by more than 5 mm and/or less than 30 mm, such as 5-30 mm (e.g., 10-30 mm, such as 10-20 mm or 20-30 mm).
- the difference between d3 and d4 is generally equal to the difference between dl and d2.
- the difference between d3 and d4 is more than 1.2 and/or less than 3 times (e.g., 1.5-2.5 times, such as about 2 times) greater than the difference between dl and d2.
- flanges 54 curve such that a tip of each flange is disposed at a shallower angle with respect to inner region 42 of upstream support portion 40, than are portions of leg 50 that are closer to downstream end 26 of frame assembly 22.
- a tip of each flange may be generally parallel with inner region 42.
- a tip portion 55 of each flange 54 that extends from the tip of the flange at least 2 mm along the flange, is disposed within 2 mm of upstream support portion 40.
- tubular portion 32 while tubular portion 32 is in its expanded state, for at least 5 percent (e.g., 5-8 percent, or at least 8 percent) of span 18 of upstream support portion 40, the upstream support portion is disposed within 2 mm of a flange 54.
- flanges 54 may pass between arms 46, and press directly against covering 23.) It is hypothesized that for some applications this configuration applies greater force to the valve tissue being sandwiched, and thereby further facilitates anchoring of the implant. That is, for some applications, distance d3 is smaller than the sum of distance d5 and a distance dl4 (described with reference to Fig. 3C).
- increasing the diameter of tubular portion 32 from dl to d2 advantageously causes flanges 54 and upstream support portion 40 to move greater than 3 mm and/or less than 25 mm (e.g., greater than 5 mm and/or less than 15 mm, e.g., 5-10 mm, such as about 7 mm) with respect to each other (e.g., toward each other and then past each other).
- upstream support portion 40 has an inner region (e.g., an inner ring) 42 that extends radially outward at a first angle with respect to axis axl (and typically with respect to tubular portion 32), and an outer region (e.g., an outer ring) 44 that extends, from the inner region, further radially outward from the tubular portion at a second angle with respect to the tubular portion, the second angle being smaller than the first angle.
- inner region e.g., an inner ring
- outer region 44 e.g., an outer ring
- inner region 42 extends radially outward at an angle alpha_l of 60-120 degrees (e.g., 70-110 degrees) with respect to axis axl
- outer region 44 extends radially outward at an angle alpha_2 of 5- 70 degrees (e.g., 10-60 degrees) with respect to axis axl.
- angles alpha_l and alpha_2 are measured between the respective region support portion 40, and the portion of axis axl that extends in an upstream direction from the level of frame assembly 22 at which the respective region begins to extend radially outward.
- implant 20 is configured to be placed at an atrioventricular valve (e.g., a mitral valve or a tricuspid valve) of the subject
- region 42 is configured to be placed against the upstream surface of the annulus of the atrioventricular valve
- region 44 is configured to be placed against the walls of the atrium upstream of the valve.
- outer region 44 is more flexible than inner region 42.
- each arm 46 may have a different structure in region 44 than in region 42. It is hypothesized that the relative rigidity of region 42 provides resistance against ventricular migration of implant 20, while the relative flexibility of region 44 facilitates conformation of upstream support portion 40 to the atrial anatomy.
- arms 46 are connected by a connector (not shown), reducing the flexibility, and/or the independence of movement of the connected arms relative to each other.
- arms 46 are connected in particular sectors of upstream support portion 40, thereby making these sectors more rigid than sectors in which the arms are not connected.
- a relatively rigid sector may be provided to be placed against the posterior portion of the mitral annulus
- a relatively flexible sector may be provided to be placed against the anterior side of the mitral annulus, so as to reduce forces applied by upstream support portion 40 on the aortic sinus.
- coupling points 52 are disposed closer to downstream end 26 of frame assembly 22 than are flanges 54, or is upstream support portion 40.
- the movement of flange 54 away from coupling point 52 facilitates the sandwiching of tissue of the native valve (e.g., leaflet and/or annulus tissue) between the flange and the upstream support portion, thereby securing implant 20 at the native valve.
- tissue of the native valve e.g., leaflet and/or annulus tissue
- a downstream end of each leg 50 is longitudinally closer than valve-frame coupling elements 31 to downstream end 36, and flange 54 of each leg is disposed longitudinally closer than the valve-frame coupling elements to upstream end 34.
- Figs. 3A-C show structural changes in frame assembly 22 during transitioning of the assembly between its compressed and expanded states, in accordance with some applications of the invention.
- Figs. 3A-C each show a portion of the frame assembly, the structural changes thereof being representative of the structural changes that occur in other portions of the frame assembly.
- FIG. 3A shows a leg 50 and struts 70 (e.g., a portion of outer frame 60), and illustrates the structural changes that occur around outer frame 60.
- Fig. 3B shows a portion of valve frame 30, and illustrates the structural changes that occur around the valve frame.
- Fig. 3C shows valve frame 30 as a whole.
- state (A) illustrates the structure while frame assembly 22 (and in particular tubular portion 32) is in its compressed state
- state (B) illustrates the structure while the frame assembly (and in particular tubular portion 32) is in its expanded state.
- Fig. 3 A shows structural changes in the coupling of legs 50 to coupling point 52 (e.g., structural changes of outer frame 60) during the transitioning of frame assembly 22 (and in particular tubular portion 32) between its compressed and expanded states.
- Each leg 50 is coupled to valve frame 30 via at least one strut 70, which connects the leg to coupling point 52.
- each leg 50 is coupled to valve frame 30 via a plurality of struts 70.
- a first end 72 of each strut 70 is coupled to leg 50, and a second end 74 of each strut is coupled to a coupling point 52.
- each leg 50 is coupled to the ring at a respective trough 62.
- Ring 66 may comprise struts 70, extending between the peaks and troughs, with each first end 72 at (or close to) a trough 62, and each second end 74 at (or close to) a peak 64.
- each strut 70 is disposed at a first angle in which first end 72 is disposed closer than second end 74 to the downstream end of the frame assembly.
- Expansion of frame assembly 22 (and in particular of tubular portion 32) toward its expanded state causes strut 70 to deflect to a second angle.
- This deflection moves first end 72 away from the downstream end of frame assembly 22. That is, in the expanded state of frame assembly 22, first end 72 is further from the downstream end of the frame assembly than it is when the frame assembly is in its compressed state. This movement is shown as a distance d5 between the position of end 72 in state (A) and its position in state (B).
- flanges 54 typically move the same distance d5 in response to expansion of frame assembly 22.
- outer frame 60 comprises ring 66
- the pattern of alternating peaks and troughs may be described as having an amplitude longitudinally between the peaks and troughs, i.e., measured parallel with central longitudinal axis axl of frame assembly 22, and the transition between the compressed and expanded states may be described as follows: In the compressed state of frame assembly 22 (and in particular of tubular portion 32), the pattern of ring 66 has an amplitude d20.
- the pattern of ring 66 has an amplitude d21 that is lower than amplitude d20. Because (i) it is at peaks 64 that ring 66 is coupled to valve frame 30 at coupling points 52, and (ii) it is at troughs 62 that ring 66 is coupled to legs 50, this reduction in the amplitude of the pattern of ring 66 moves legs 50 (e.g., flanges 54 thereof) longitudinally further from the downstream end of the frame assembly. The magnitude of this longitudinal movement (e.g., the difference between magnitudes d20 and d21) is equal to d5.
- distance d5 is the same distance as the distance that flange 54 moves away from coupling point 52 during expansion of the frame assembly. That is, a distance between flange 54 and the portion of leg 50 that is coupled to strut 70, typically remains constant during expansion of the frame assembly.
- the longitudinal movement of flange 54 away from coupling point 52 is a translational movement (e.g., a movement that does not include rotation or deflection of the flange).
- a distance d7, measured parallel to axis axl, between coupling point 52 and first end 72 of strut 70 while assembly 22 is in its expanded state is 1-5 mm (e.g., 1-4 mm).
- amplitude d20 is 2-10 mm (e.g., 4-7 mm).
- amplitude d21 is 4-9 mm (e.g., 5-7 mm).
- first end 72 of strut 70 is disposed closer to the downstream end of frame assembly 22 than is coupling point 52.
- first end 72 of strut 70 is disposed further from the downstream end of frame assembly 22 than is coupling point 52.
- frame assembly 22 For applications in which frame assembly 22 comprises a plurality of legs 50 and a plurality of coupling points 52 (e.g., for applications in which the frame assembly comprises outer frame 60) expansion of the frame assembly increases a circumferential distance between adjacent coupling points 52, and an increase in a circumferential distance between adjacent legs 50.
- Fig. 3A shows such an increase in the circumferential distance between adjacent coupling points 52, from a circumferential distance d8 in the compressed state to a circumferential distance d9 in the expanded state.
- distance d8 is 1-6 mm.
- distance d9 is 3-15 mm.
- legs 50 are also connected to each other via connectors 78.
- Connectors 78 allow the described movement of legs 50 during expansion of frame assembly 22, but typically stabilize legs 50 relative to each other while the frame assembly is in its expanded state. For example, connectors 78 may bend and/or deflect during expansion of the frame assembly.
- FIGs. 3B-C show structural changes in valve frame 30 during the transitioning of frame assembly 22 between its compressed and expanded states.
- Tubular portion 32 of valve frame 30 is defined by a plurality of cells 80, which are defined by the repeating pattern of the valve frame.
- cells 80 When frame assembly 22 is expanded from its compressed state toward its expanded state, cells 80 (i) widen from a width d 10 to a width dl 1 (measured orthogonal to axis axl of the frame assembly), and (ii) shorten from a height dl2 to a height dl3 (measured parallel to axis axl of the frame assembly).
- This shortening reduces the overall height (i.e., a longitudinal length between upstream end 34 and downstream end 36) of tubular portion 32 from a height d22 to a height d23, and thereby causes the above-described longitudinal movement of upstream support portion 40 toward coupling points 52 by a distance dl4 (shown in Fig. 3C).
- coupling points 52 are disposed at the widest part of each cell.
- implant 20 comprises:
- valve frame (30) that comprises a tubular portion (32) that circumscribes a longitudinal axis (axl) of the valve frame so as to define a lumen (38) along the axis, the tubular portion having an upstream end (34), a downstream end (36), a longitudinal length therebetween, and a diameter (e.g., dl or d2) transverse to the longitudinal axis; a valve member (58), coupled to the tubular portion, disposed within the lumen, and arranged to provide unidirectional upstream-to-downstream flow of blood through the lumen;
- the implant has a first state (e.g., as shown in Fig. 2D and Fig. 4D) and a second state (e.g., as shown in Fig. 2E and Fig. 4E),
- the upstream support portion extends radially outward from the tubular portion
- the tissue-engaging flange extends radially outward from the tubular portion
- the tubular portion, the upstream support portion, and the outer frame are arranged such that transitioning of the implant from the first state toward the second state:
- a diameter-increase amount e.g., the difference between dl and d2
- a length-decrease amount e.g., the difference between d22 and d23
- the flange moves the flange a longitudinal distance with respect to (e.g., toward or toward-and-beyond) the upstream support portion (e.g., the difference between d3 and d4), this distance being greater than the length-decrease amount.
- valve frame 30 is typically coupled to outer frame 60 by coupling between (i) a valve-frame coupling element 31 defined by valve frame 30, and (ii) an outer- frame coupling element 61 defined by outer frame 60 (e.g., an outer-frame coupling element is coupled to end 74 of each strut).
- elements 31 and 61 are fixed with respect to each other.
- Each coupling point 52 is thereby typically defined as the point at which a valve-frame coupling element and a corresponding outer-frame coupling element 61 are coupled (e.g., are fixed with respect to each other).
- elements 31 and 61 are eyelets configured to be coupled together by a connector, such as a pin or a stitch (e.g., a suture).
- a connector such as a pin or a stitch (e.g., a suture).
- the fixing of elements 31 and 61 with respect to each other may be achieved by welding, soldering, crimping, stitching (e.g., suturing), gluing, or any other suitable technique.
- valve-frame coupling elements 31 are defined by tubular portion 32, and are disposed circumferentially around central longitudinal axis axl.
- Outer- frame coupling elements 61 are coupled to ring 66 (or defined by frame 60, such as by ring 66) at respective peaks 64.
- valve frame 30 e.g., tubular portion 32 thereof
- outer frame 60 e.g., ring 66 thereof
- a radial gap dl9 between valve frame 30 (e.g., tubular portion 32 thereof) and outer frame 60 (e.g., ring 66 thereof) is typically less than 2 mm (e.g., less than 1 mm), in both the compressed and expanded states, and during the transition therebetween.
- more than 50 percent (e.g., more than 60 percent) of ring 66 is disposed within 2 mm of tubular portion 32 in both the compressed and expanded states, and during the transition therebetween.
- more than 50 percent (e.g., more than 60 percent) of outer frame 60, except for flanges 54, is disposed within 2 mm of tubular portion 32 in both the compressed and expanded states, and during the transition therebetween.
- frame assembly 22 e.g., to outer frame 60 thereof
- outer frame 60 the structural changes to frame assembly 22 (e.g., to outer frame 60 thereof) are described hereinabove as they occur during (e.g., as a result of) expansion of the frame assembly (in particular tubular portion 32 thereof). This is the natural way to describe these changes because, as described hereinbelow with respect to Figs. 4A-6, assembly 22 is in its compressed state during percutaneous delivery to the implant site, and is subsequently expanded.
- implant 20 may be further understood by describing structural changes that occur during compression of the frame assembly (e.g., a transition from the expanded state in Fig. 2E to the intermediate state in Fig.
- tubular portion 32 thereof in particular tubular portion 32 thereof (including if tubular portion 32 were compressed by application of compressive force to the tubular portion, and not to frame 60 except via the tubular portion pulling frame 60 radially inward).
- implant 20 is typically compressed (i.e., "crimped") soon before its percutaneous delivery, and therefore these changes may occur while implant 20 is in the care of the operating physician.
- the fixation of peaks 64 to respective sites of tubular portion 32 is such that compression of the tubular portion from its expanded state toward its compressed state such that the respective sites of the tubular portion pull the peaks radially inward via radially-inward tension on coupling points 52: (i) reduces a circumferential distance between each of the coupling points and its adjacent coupling points (e.g., from d9 to d8), and (ii) increases the amplitude of the pattern of ring 66 (e.g., from d21 to d20).
- the fixation of outer-frame coupling elements 61 to valve- frame coupling elements 31 is such that compression of tubular portion 32 from its expanded state toward its compressed state such that the valve-frame coupling elements pull the outer- frame coupling elements radially inward: (i) reduces a circumferential distance between each of the outer-frame coupling elements and its adjacent outer-frame coupling elements (e.g., from d9 to d8), and (ii) increases the amplitude of the pattern of ring 66 (e.g., from d21 to d20).
- the fixation of peaks 64 to the respective sites of tubular portion 32 is such that compression of the tubular portion from its expanded state toward its compressed state (i) pulls the peaks radially inward via radially-inward pulling of the respective sites of the tubular portion on the peaks, (ii) reduces a circumferential distance between each of coupling points 52 and its adjacent coupling points (e.g., from d9 to d8), and (iii) increases the amplitude of the pattern of ring 66 (e.g., from d21 to d20), without increasing radial gap dl9 between valve frame 30 (e.g., tubular portion 32 thereof) and the ring by more than 1.5 mm.
- the fixation of outer- frame coupling elements 61 with respect to valve-frame coupling elements 31 is such that compression of tubular portion 32 from its expanded state toward its compressed state (i) pulls outer-frame coupling elements 61 radially inward via radially-inward pulling of valve-frame coupling elements 31 on outer- frame coupling elements 61, (ii) reduces a circumferential distance between each of the outer-frame coupling elements and its adjacent outer-frame coupling elements (e.g., from d9 to d8), and (iii) increases the amplitude of the pattern of ring 66 (e.g., from d21 to d20), without increasing radial gap dl9 between valve frame 30 (e.g., tubular portion 32 thereof) and the ring by more than 1.5 mm.
- FIGs. 4A-F are schematic illustrations of implantation of implant 20 at a native valve 10 of a heart 4 of a subject, in accordance with some applications of the invention.
- Valve 10 is shown as a mitral valve of the subject, disposed between a left atrium 6 and a left ventricle 8 of the subject.
- implant 20 may be implanted at another heart valve of the subject, mutatis mutandis.
- Figs. 4A-F show implant 20 being delivered trans sep tally via a sheath 88, the implant may alternatively be delivered by any other suitable route, such as transatrially, or transapically.
- Implant 20 is delivered, in its compressed state, to native valve 10 using a delivery tool 89 that is operable from outside the subject (Fig. 4A).
- implant 20 is delivered within a delivery capsule 90 of tool 89, which retains the implant in its compressed state.
- a transseptal approach such as a transfemoral approach, is shown.
- implant 20 is positioned such that at least flanges 54 are disposed downstream of the native valve (i.e., within ventricle 8).
- frame assembly 22 of implant 20 is as shown in Fig. 2A.
- flanges 54 are allowed to protrude radially outward, as described hereinabove, e.g., by releasing them from capsule 90 (Fig. 4B).
- capsule 90 may comprise a distal capsule -portion 92 and a proximal capsule-portion 94, and the distal capsule-portion may be moved distally with respect to implant 20, so as to expose flanges 54.
- frame assembly 22 of implant 20 is as shown in Fig. 2B.
- implant 20 is moved upstream, such that upstream support portion 40, in its compressed state, is disposed upstream of leaflets 12 (i.e., within atrium 6).
- upstream movement of implant 20 causes flanges 54 to engage leaflets 12.
- Upstream support portion 40 is then allowed to expand such that it protrudes radially outward, as described hereinabove, e.g., by releasing it from capsule 90 (Fig. 4D).
- proximal capsule -portion 94 may be moved proximally with respect to implant 20, so as to expose upstream support portion 40.
- frame assembly 22 of implant 20 is as shown in Fig. 2D, in which: (i) distance d3 exists between upstream support portion 40 and flanges 54, (ii) the flanges have span dl5, (iii) the upstream support portion has span dl7, and (iv) tubular portion 32 has diameter dl.
- expansion of frame assembly 22 is inhibited by distal capsule-portion 92
- implant 20 is allowed to expand toward its expanded state, such that tubular portion 32 widens to diameter d2, and the distance between upstream support portion 40 and flanges 54 reduces to distance d4 (Fig. 4E).
- tissue of valve 10 typically including annular tissue and/or leaflets 12
- Fig. 4F shows delivery capsule 90 having been removed from the body of the subject, leaving implant 20 in place at valve 10.
- implant 20 is configured such that when tubular portion 32 is expanded, flanges 54 and upstream support portion 40 move a relatively large distance toward each other. This enables distance d3 to be relatively large, while distance d4 is sufficiently small to provide effective anchoring. As also described hereinabove, implant 20 is configured such that flanges 54 and upstream support portion 40 can extend radially outward a relatively large distance while tubular portion 32 remains compressed. It is hypothesized that for some applications, these configurations (independently and/or together) facilitate effective anchoring of implant 20, by facilitating placement of a relatively large proportion of valve tissue (e.g., leaflets 12) between the flanges and the upstream support portion prior to expanding tubular portion 32 and sandwiching the valve tissue.
- valve tissue e.g., leaflets 12
- valve tissue e.g., leaflets 12
- this configuration of implant 20 facilitates identifying correct positioning of the implant (i.e., with upstream support portion 40 upstream of leaflets 12 and flanges 54 downstream of the leaflets) prior to expanding tubular portion 32 and sandwiching the valve tissue.
- implant 20 defines a toroidal space 49 between flanges 54 and upstream support portion 40 (e.g., a space that is wider than distance d4).
- space 49 may have a generally triangular cross-section. It is hypothesized that for some such applications, in addition to sandwiching tissue of the native valve between upstream support portion 40 and flanges 54 (e.g., the tips of the flanges), space 49 advantageously promotes tissue growth therewithin (e.g., between leaflet tissue and covering 23), which over time further secures implant 20 within the native valve.
- FIG. 5 is a schematic illustration of a step in the implantation of implant 20, in accordance with some applications of the invention.
- Figs. 4A-F show an implantation technique in which flanges 54 are expanded prior to upstream support portion 40, for some applications the upstream support portion is expanded prior to the flanges.
- Fig. 5 shows a step in such an application.
- implant 20 may be implanted by causing flanges 54 to radially protrude before causing upstream support portion 40 to radially protrude, or may be implanted by causing the upstream support portion to protrude before causing the flanges to protrude.
- implant 20 is thereby configured to be deliverable in a downstream direction (e.g., trans septally, as shown, or transapically) or in an upstream direction (e.g., transapically or via the aortic valve).
- an operating physician may decide which delivery route is preferable for a given application (e.g., for a given subject, and/or based on available equipment and/or expertise), and implant 20 is responsively prepared for the chosen delivery route (e.g., by loading the implant into an appropriate delivery tool).
- downstream delivery of implant 20 may be performed by expanding flanges 54 first (e.g., as shown in Figs. 4A-F) or by expanding upstream support portion 40 first (e.g., as shown in Fig. 5).
- upstream delivery of implant 20 may be performed by upstream support portion 40 first, or by expanding flanges 54 first.
- FIG. 6 is a schematic illustration of implant 20, in the state and position shown in Fig. 4D, in accordance with some applications of the invention.
- leaflets 12 of valve 10 are able to move, at least in part in response to beating of the heart.
- Frame (A) shows leaflets 12 during ventricular systole
- frame (B) shows the leaflets during ventricular diastole.
- blood is thereby able to flow from atrium 6 to ventricle 8, between leaflets 12 and implant 20.
- imaging techniques may be used to verify the position of implant 20, and/or positioning of leaflets 12 between upstream support portion 40 and flanges 54.
- FIGS. 7A-B and 8A-B are schematic illustrations of frame assemblies 122 and 222 of respective implants, in accordance with some applications of the invention. Except where noted otherwise, frame assemblies 122 and 222 are typically identical to frame assembly 22, mutatis mutandis. Elements of frame assemblies 122 and 222 share the name of corresponding elements of frame assembly 22. Additionally, except where noted otherwise, the implants to which frame assemblies 122 and 222 belong are similar to implant 20, mutatis mutandis.
- Frame assembly 122 comprises (i) a valve frame 130 that comprises a tubular portion
- outer frame 160 that circumscribes the valve frame, and comprises a plurality of legs 150 that each comprise a tissue-engaging flange 154.
- outer frame 160 comprises a ring 166 to which legs 150 are coupled. Ring 166 is defined by a pattern of alternating peaks and troughs, the peaks being fixed to frame 130 at respective coupling points 152, e.g., as described hereinabove for frame assembly 22, mutatis mutandis.
- Frame assembly 222 comprises (i) a valve frame 230 that comprises a tubular portion 232 and an upstream support portion 240 that typically comprises a plurality of arms 246, and (ii) an outer frame (e.g., a leg frame) 260 that circumscribes the valve frame, and comprises a plurality of legs 250 that each comprise a tissue-engaging flange 254.
- outer frame 260 comprises a ring 266 to which legs 250 are coupled. Ring 266 is defined by a pattern of alternating peaks and troughs, the peaks being fixed to frame 230 at respective coupling points 252, e.g., as described hereinabove for frame assembly 22, mutatis mutandis.
- tubular portions 32, 132 and 232 are each defined by a repeating pattern of cells that extends around the central longitudinal axis. Typically, and as shown, tubular portions 32, 132 and 232 are each defined by two stacked, tessellating rows of cells. In the expanded state of each tubular portion, these cells are typically narrower at their upstream and downstream extremities than midway between these extremities. For example, and as shown, the cells may be roughly diamond or astroid in shape.
- each arm 46 is attached to and extends from a site 35 that is at the upstream extremity of cells of the upstream row.
- each arm 146 or 246 is attached to and extends from a site 135 (assembly 122) or 235 (assembly 222) that is at the connection between two adjacent cells of the upstream row (alternatively described as being at the upstream extremity of cells of the downstream row).
- this lower position of the arms while maintaining the length of the lumen of the tubular portion, advantageously reduces the distance that the tubular portion (i.e., the downstream end thereof) extends into the ventricle of the subject, and thereby reduces a likelihood of inhibiting blood flow out of the ventricle through the left ventricular outflow tract. It is further hypothesized that this position of the arms reduces radial compression of the tubular portion by movement of the heart, due to greater rigidity of the tubular portion at sites 135 and 235 (which is supported by two adjacent cells) than at site 35 (which is supported by only one cell).
- the legs are circumferentially staggered with the arms of the upstream support portion (46, 146 and 246, respectively). This allows the legs to move in an upstream direction between the arms during expansion of the tubular portion (32, 132 and 232, respectively), facilitating application of greater sandwiching force on tissue of the native valve.
- the lower position of the arms of assemblies 122 and 222 includes circumferentially shifting the position of the arms by the width of half a cell. In order to maintain the circumferential staggering of the arms and legs, rings 166 and 266 (and thereby legs 150 and 250) are circumferentially shifted correspondingly.
- the peaks of rings 166 and 266 are generally aligned midway between these sites (i.e., at spaces of the cellular structure of the tubular portion). Appendages 168 (for assembly 122) or 268 (for assembly 222) facilitate fixing of the peak with respect to the tubular structure.
- appendages 168 are defined by valve frame 130 (e.g., by tubular portion 132 thereof) and extend (in a downstream direction) to the peaks of ring 166, to which they are fixed.
- each appendage 168 may define a valve-frame coupling element 131 that is fixed to a respective outer- frame coupling element 161 defined by outer frame 260.
- appendages 168 extend from sites 135.
- appendages 168 are integral with tubular portion 132 and/or in-plane with the tubular portion (e.g., are part of its tubular shape).
- appendages 268 are defined by outer frame 260, and extend (e.g., in an upstream direction) from the peaks of ring 266.
- appendages 268 extend to sites 235, to which they are fixed.
- each appendage 268 may define an outer- frame coupling element 261 that is fixed to a respective valve-frame coupling element 231 defined by valve frame 230 (e.g., by tubular portion 232 thereof).
- appendages 268 are integral with outer frame 260 and/or in-plane with adjacent portions of outer frame 260, such as ring 266. Therefore, frame assembly 122 defines a hub at site 135, and frame assembly 222 defines a hub at site 235.
- apparatus therefore comprises: a plurality of prosthetic valve leaflets; and
- a frame assembly comprising:
- tubular portion (132 or 232) defined by a repeating pattern of cells, the tubular portion extending circumferentially around longitudinal axis axl so as to define a longitudinal lumen, the prosthetic valve leaflets coupled to the inner frame and disposed within the lumen;
- an outer frame (160 or 260), comprising a plurality of legs (150 or 250), distributed circumferentially around the tubular portion, each leg having a tissue-engaging flange (154 or 254);
- an upstream support portion (140 or 240) that comprises a plurality of arms (146 or 246) that extend radially outward from the tubular portion; and a plurality of appendages (168 or 268), each having a first end that defines a coupling element (161 or 261) via which the tubular portion is coupled to the outer frame, and a second end;
- the frame assembly defines a plurality of hubs (135 or 235), distributed circumferentially around the longitudinal axis on a plane that is transverse to longitudinal axis axl, each hub defined by convergence and connection of, (i) two adjacent cells of the tubular portion, (ii) an arm of the plurality of arms, and (iii) an appendage of the plurality of appendages.
- FIGs. 9A-C are schematic illustrations of an implant 320 comprising a frame assembly 322, in accordance with some applications of the invention. Except where noted otherwise, frame assembly 322 is identical to frame assembly 122, and implant 300 is identical to the implant to which frame assembly 122 belongs, mutatis mutandis.
- Fig. 9A is a side-view of implant 320
- Fig. 9B is an isometric bottom-view of the implant.
- Frame assembly 122 comprises (i) a valve frame 330 that comprises a tubular portion
- outer frame 360 that circumscribes the valve frame, and comprises a plurality of legs 350 that each comprise a tissue-engaging flange 354.
- outer frame 360 comprises a ring 366 to which legs 350 are coupled.
- Ring 366 is defined by a pattern of alternating peaks and troughs, the peaks being fixed to frame 330 at respective coupling points 352, e.g., as described hereinabove for frame assembly 22 and/or frame assembly 122, mutatis mutandis.
- Frame assembly 322 comprises an annular upstream support portion 340 that has an inner portion 342 that extends radially outward from the upstream portion (e.g., the upstream end) of tubular portion 332.
- Upstream support portion 340 further comprises one or more fabric pockets 344 disposed circumferentially around inner portion 342, each pocket of the one or more pockets having an opening that faces a downstream direction (i.e., generally toward the downstream end of implant 320).
- upstream support portion 340 has a single toroidal pocket 344 that extends circumferentially around inner portion 342.
- a covering 323 e.g., similar to covering 23, described hereinabove, mutatis mutandis
- arms 346 are shaped to form pocket 344 from covering 323. For example, and as shown, arms 346 may curve to form a hook-shape.
- portion 340 has a plurality of separate pockets 344, e.g., separated at arms 346.
- covering 323 is loosely-fitted (e.g., baggy) between radially-outward parts of arms 346, e.g., compared to inner portion 342, in which the covering is more closely-fitted between radially-inward parts of the arms.
- FIG. 9C shows implant 320 implanted at native valve 10.
- Pocket 344 is typically shaped and arranged to billow in response to perivalvular flow 302 of blood in an upstream direction. If ventricular systole forces blood in ventricle 8 between implant 320 and native valve 10, that blood inflates pocket 344 and presses it (e.g., covering 323 and/or the radially- outward part of arm 346) against tissue of atrium 6 (e.g., against the atrial wall), thereby increasing sealing responsively. It is hypothesized by the inventors that the shape and orientation of pocket 344 (e.g., the hook-shape of arms 346) facilitates this pressing radially- outward in response to the pocket's receipt of upstream-flowing blood.
- the shape and orientation of pocket 344 e.g., the hook-shape of arms 346
- Pocket(s) 344 may be used in combination with any of the implants described herein, mutatis mutandis.
- Fig. 10 is a schematic illustration of a frame assembly 422 of an implant, in accordance with some applications of the invention. Except where noted otherwise, frame assembly 422 is typically identical to frame assembly 122, mutatis mutandis. Elements of frame assembly 422 share the name of corresponding elements of frame assembly 122. Additionally, except where noted otherwise, the implant to which frame assembly 422 belongs is similar to implant the other implants described herein (e.g., implant 20), mutatis mutandis. Fig. 10 shows frame assembly 422 in an expanded state (e.g., in the absence of external deforming forces, such as those provided by a delivery tool during implantation, or by heart tissue after implantation).
- an expanded state e.g., in the absence of external deforming forces, such as those provided by a delivery tool during implantation, or by heart tissue after implantation.
- Frame assembly 422 comprises (i) a valve frame (e.g., an inner frame) 430 that comprises a tubular portion 432 and an upstream support portion 440 that typically comprises a plurality of radial arms 446, and (ii) an outer frame (e.g., a leg frame) 460 that circumscribes the valve frame, and comprises a plurality of legs 450 that each comprise a tissue-engaging flange 454.
- outer frame 460 comprises a ring 466 to which legs 450 are coupled.
- Ring 466 is defined by a pattern of alternating peaks and troughs, the peaks being fixed to frame 430 at respective coupling points 452, e.g., as described hereinabove for frame assemblies 22 and 122, mutatis mutandis.
- Tubular portion 432 has a diameter d26 (corresponding to diameter d2 of implant 20), and a transverse cross- sectional area that is a function of diameter d26.
- legs 450 are circumferentially staggered with arms 446 of upstream support portion 440.
- FIG. 10 shows frame assembly 422 in its expanded state, in which upstream support portion 440 (e.g., arms 446) and flanges 454 extend radially outward from tubular portion 432, and intersect at an intersection 470. Opposite intersections 470 define an intersect diameter d27.
- upstream support portion 440 e.g., arms 446
- flanges 454 extend radially outward from the tubular portion and toward the upstream support portion 440 (i.e., outward and in an upstream direction).
- a toroidal space 449 is defined between flanges 454, upstream support portion 440, and tubular portion 432, the toroidal space circumscribing the tubular portion.
- the implant to which frame assembly 422 belongs is secured at the native valve by sandwiching heart tissue (e.g., leaflets 12 and/or the valve annulus) between upstream support portion 440 and flanges 54 (e.g., within space 449).
- heart tissue e.g., leaflets 12 and/or the valve annulus
- leaflets 12 are trapped in space 449.
- Space 449 is dimensioned to be sufficiently large to accommodate leaflets 12, because it has been observed by the inventors that if space 449 is too small, the implant tends to become secured to tissue that is suboptimally close to the middle of the native valve orifice (e.g., closer to the free edges of the leaflets), and to sit in a position that is suboptimally downstream (i.e., into ventricle 8). Additionally, space 449 is dimensioned to be sufficiently small to accommodate leaflets 12 snugly, because it has been observed by the inventors that if space 449 is sufficiently small that the leaflets fill the space well (typically folding or bunching up within the space), sandwiching forces are applied to leaflet tissue throughout space 449.
- space 449 is too large, sandwiching forces may be applied to the leaflets only at or close to intersections 470, reducing the effectiveness of anchoring, and/or increasing a likelihood of damaging the tissue at or close to the intersections.
- an optimal size of space 449 i.e., a size that is sufficiently large to accommodate leaflets 12, but sufficiently small to do so snugly
- the space has a cross-sectional area 451 that is 5-10 percent (e.g., 5-8 percent, such as 6-7 percent or 6.5-7.5 percent) of the transverse cross- sectional area of tubular portion 432.
- this relative size is optimal across implants that have tubular portions of different diameters. For example:
- an optimally- sized cross-sectional area 451 may be 25-40 (e.g., about 35) mm A 2.
- an optimally- sized cross-sectional area 451 may be 30-45 (e.g., about 40) mm A 2.
- an optimally- sized cross-sectional area 451 may be 35-50 (e.g., about 45) mm A 2. This optimal relative size range of area 451 is hypothesized by the inventors to apply to implants that have tubular portions that are narrower or wider than the above examples (e.g., 23 mm or 31 mm diameter).
- implants of different diameters d26 are provided, and each of the implants has a cross- sectional area 451 that is 5-10 percent (e.g., 5-8 percent, such as 6- 7 percent or 6.5-7.5 percent) of the transverse cross- sectional area of the tubular portion 432 of the implant.
- the tubular portion 432 of one of the implants may have a have transverse cross- sectional area that is at least 15 percent (e.g., at least 30 percent) greater than another one of the implants.
- Tubular portion 432 has an upstream end 434 and a downstream end 436.
- arms 446 are attached to and extend from sites 435 that are downstream of upstream end 434, e.g., at the connection between two adjacent cells of the upstream row of cells of tubular portion 432 (alternatively described as being at the upstream extremity of cells of the downstream row of cells).
- each arm 446 defines, respectively: (i) an ascending portion 446a that extends in an upstream direction past upstream end 434 of tubular portion 432 (e.g., by a distance d28), (ii) an arch portion 446b that curves in a downstream direction to form an arch (portion 446b may alternatively be described as being convex in an upstream direction), and (iii) a lateral portion 446c that curves in an upstream direction.
- arch portion 446b curves in the downstream direction as far as (and typically past) tips 455 of flanges 454 (i.e., at the arch portion, each arm 446 extends below (i.e., further downstream than) adjacent tips 455).
- intersections 470 are generally close to where arms 446 begin to curve upstream.
- a height d29 is the height, along the central longitudinal axis of the implant, between (i) the crest of arch portion 446b, and (ii) intersection 470.
- height d29 is 0.5-3.5 mm (e.g., 1.8-2.6 mm).
- a height d30 is the height, along the central longitudinal axis of the implant, between (i) the crest of arch portion 446b, and (ii) site 435.
- height d30 is 4- 7.5 mm (e.g., 5.2-6.5 mm).
- arms 446 extend (i) radially outward and above (a) upstream end 434 and (b) the tips of flanges 454, and then (ii) further radially outward and below (a) upstream end 434 and/or (b) the tips of flanges 454 (i.e., toward the flanges).
- the above configuration of arm 46 increases the size of toroidal space 449 (compared to a similar arm in which d28 and/or d29 are smaller), e.g., providing an optimal cross-sectional area 451, as described hereinabove.
- the arms do not have arch portions that extend above (i) the upstream end of the respective tubular portion, or (ii) the tips of the respective flanges.
- the lateral portions of these arms do extend upwardly, the lateral portions are radially outward of the flanges, and therefore do not increase the cross-sectional area of the toroidal space defined by these frame assemblies.
- an end 446d (i.e., the lateral extremity) of arm 446 is disposed further in an upstream direction than arch portion 446b.
- the outer stent frame (e.g., leg frame) 460 has a radial thickness d24 (i.e., a thickness measured along an axis that extends radially outward from the central longitudinal axis of the implant) that is greater than a radial thickness d25 of inner stent frame (e.g., valve frame) 430. That is, the outer stent frame is radially thicker than the inner stent frame.
- first wall thickness e.g., equal to d25
- second wall thickness e.g., equal to d24
- other methods of manufacture including 3D printing, may be used.
- thickness d24 is at least 10 percent (e.g., at least 20 percent, such as at least 30 percent) and/or no more than 80 percent (e.g., no more than 50 percent) greater than thickness d25.
- thickness d24 is 0.6-0.8 mm (e.g., 0.7- 0.75 mm, e.g., 0.71-0.73 mm, such as 0.72 mm)
- thickness d25 is 0.45-0.65 mm (e.g., 0.5-0.55 mm, e.g., 0.52-0.54 mm, such as 0.53 mm).
- outer stent frame e.g., leg frame
- inner stent frame e.g., valve frame
- apparatus comprising:
- a frame assembly transluminally advanceable to the heart, and comprising:
- the inner stent frame is cut from a first tube of nitinol that has a first-tube wall thickness
- the outer stent frame is cut from a second tube of nitinol that has a second-tube wall thickness that is greater than the first-tube wall thickness
- Providing a frame assembly in which the outer frame has greater radial thicknesses is hypothesized by the inventors to advantageously provide (i) radially-expansive strength (and resistance to radially-inward deformation) to the portion of the frame assembly in which the prosthetic leaflets are disposed, and (ii) rigidity (and resistance to fatigue) to legs 450.
- tubular portion 432 defines an inner-stent-frame relaxed expanded diameter (which is measured as an outer diameter of the tubular portion) that is greater than an outer- stent- frame relaxed expanded diameter defined by ring 466 (which is measured as an inner diameter of the ring).
- the inner-stent-frame relaxed expanded diameter is 0.5-1.5 (e.g., 0.5-1, such as 0.8) mm greater than the outer- stent- frame relaxed expanded diameter.
- frame 460 constrains tubular portion 432 to an inner-stent-frame constrained expanded diameter that is smaller than the inner-stent-frame relaxed expanded diameter. Therefore, even in the relaxed expanded state of frame assembly 422 (i.e., the state shown in Fig. 10), residual stress is typically present in frame 430 (e.g., tubular portion 432 thereof) and/or frame 460 (e.g., ring 466 thereof). Additionally, when the frame assembly is in its compressed state, and throughout its expansion into its expanded state, circumferential contact (and reciprocating expansive and compressive forces) is maintained between frame 460 and tubular portion 432.
- this optional residually-stressed configuration advantageously increases the strength of the frame assembly (e.g., the tubular portion), and in particular its resistance to deformation, e.g., in response to forces applied directly to the frame assembly by tissue of the native valve, and/or applied indirectly to the frame assembly during systole when ventricular blood is forced against the prosthetic leaflets, which pull on the frame assembly.
- frames 430 and 460 are fixed to each other independently of any additional coupling that might be provided by the residually- stressed configuration.
- the frames are fixed to each other at coupling points 452, e.g., by welding, soldering, crimping, stitching (e.g., suturing), gluing, or any other suitable technique.
- the frames are also fixed to each other at commissures of the implant. That is, the residually-stressed configuration is provided for strength and rigidity of the frame assembly (and for ensuring maintenance of circumferential contact between the frames), rather than for coupling of the frames to each other.
- FIGs. 11A-C are schematic illustrations of a connector 510 and a commissure 500 of a prosthetic valve, in accordance with some applications of the invention.
- Connector 510 typically comprises a flexible sheet 512 that is folded to define elements of the connector. Further typically, sheet 512 is a single, unitary sheet (e.g., cut from a single piece of stock material, such as a fabric).
- Fig. 11A shows two perspective views of connector 510 (e.g., sheet 512 thereof) in its folded state, and Fig. 11B shows its unfolded state.
- Fig. 11C shows connector 510 fixed to frame assembly 422 at commissure 500. Commissure 500 is described with respect to the implant to which frame assembly 422 belongs, although it may be used in combination with the other prosthetic valves described herein, and/or with other prosthetic valves, mutatis mutandis.
- the implant to which frame assembly 422 belongs defines a plurality of commissures 500 at which two of the prosthetic leaflets of the implant (e.g., leaflets 58 or similar) meet, and are fixed to the frame assembly.
- the implant comprises a plurality of stitches (e.g., sutures) 502, via which commissural portions of the two prosthetic leaflets are secured to the frame assembly.
- the stitches secure the prosthetic leaflets to the inner stent frame (frame 430, e.g., tubular portion 432 thereof) and to the outer stent frame (frame 460). That is, the leaflets are not coupled to the outer stent frame merely by being fixed to the inner stent frame, which in turn is coupled to the outer stent frame.
- the leaflets are fixed to both frames by stitches 502. Because (as described hereinabove) (i) frame 460 is radially thicker than frame 430, and (ii) the relative diameters of the frames results in residual stress and maintained circumferential contact between frames 430 and 460, the fixation of the leaflets to both frames advantageously provides the implant with enhanced resistance to pulling of commissures 500 radially inward by the prosthetic leaflets when ventricular pressure increases during ventricular systole.
- connector 510 typically comprising primarily or solely a fabric
- Connector 510 is shaped to define a plurality of flaps 504, and a leaflet-receptacle 514 comprising one or more (e.g., two) leaflet-engaging tabs 506, such as a first leaflet-engaging tab 506a and a second leaflet-engaging tab 506b.
- connector 510 is shaped to define a panel (e.g., a plate) 508, tabs 506 protrude from of one side of the panel, and each flap 504 folds over a respective portion of the other side of the panel.
- leaflet-engaging tabs 506 e.g., to respective leaflet-engaging tabs.
- Flaps 504 are stitched to frames 430 and 460 - i.e., are fixed to the frames by stitches 502.
- flaps 504 are folded over or wrapped around elements of frames 430 and 460, and are fixed in this disposition by stitches 502, thereby providing increased strength to the fixation of the leaflets to the frames (and of the frames to each other).
- connector 510 comprises four flaps 504.
- flaps 504 are arranged in a circuit such that each flap has two adjacent flaps around the circuit, and the fold axis ax2 of each flap is oriented at 60-120 degrees (e.g., 70-110 degrees, e.g., 80-100 degrees) from the fold axis of each of its adjacent flaps.
- the frame to which connector 510 is to be connected has a cellular structure with roughly diamond-shape cells, such an arrangement facilitates attachment of the connector to the frame.
- connector 510 has four flaps arranged roughly in a diamond shape, with two upstream flaps 504a tapering away from each other in a downstream direction, and two downstream flaps 504b tapering toward each other in a downstream direction.
- Each upstream flap 504a is typically folded over or wrapped around an element of frame 430 and an element of frame 460.
- FIG. l lC at commissure 500, elements of frame 430 align with elements of frame 460, and flaps 504a are arranged to align with these elements of both frames. Flaps 504 are folded over or wrapped around these elements of both frames, and are fixed to these elements by stitches 502.
- downstream flaps 504b In the position of downstream flaps 504b, elements of frame 430 do not align with elements of frame 460, and may even be perpendicular to them.
- Downstream flaps 504b are arranged to align with elements of frame 430, and are folded over or wrapped around elements, but typically not over or around elements of frame 460.
- the elements of frame 430, and flaps 504b, are stitched to elements of frame 460; these stitches are indicated by the reference numeral 502b, while the stitches that secure flaps over or around frame elements are indicated by the reference numeral 502a.
- panel 508 is also stitched to elements of frame 430 and/or frame 460; these stitches are indicated by the reference numeral 502c.
- frames 430 and 460 are thereby fixed to each other at commissures 500 (i.e., in addition to at coupling points 452).
- connector 510 and/or the stitches may secure the leaflets only to inner frame 430, such that the leaflets are coupled to outer frame 460 only via inner frame 430.
- a connector comprising a flexible sheet (e.g., sheet 512) that is folded to define: (i) a panel (e.g., panel 508) that has a first side (e.g., side 508a), and a second side (e.g., side 508b) that is opposite the first side; (ii) a leaflet receptacle (e.g., receptacle 514), disposed on the first side of the panel, and protruding in the first direction away from the panel; and (iii) a plurality of flaps (e.g., flaps 504), each flap folded about a respective fold axis (e.g., axis ax2) such that at least part of each flap is disposed on the second side of the panel.
- a panel e.g., panel 508
- a leaflet receptacle e.g., receptacle 514
- flaps e.g., flaps 504
- Receptacle 514 is configured to sandwich one or more prosthetic leaflets between leaflet-engaging tabs 506a and 506b.
- stitching holes 516 are defined in leaflet- engaging tabs 506 to guide the introduction of stitches which will secure the leaflets sandwiched between the tabs.
- holes 516 are arranged into rows.
- each leaflet-engaging tab 506 may define a first row 518a of stitching holes and a second row 518b of stitching holes, the rows of one tab being aligned with the rows of the other tab.
- rows 518a and 518b diverge from each other at an angle alpha_3, typically such that that progressively downstream parts of the rows are progressively further from each other.
- angle alpha_3 may be 10-45 degrees (e.g., 10-30 degrees, e.g., 15-25 degrees, such as about 20 degrees).
- sheet 512 is folded such that each leaflet-engaging tab 506 comprises an outer layer 520o, and an inner layer 520i that is positioned to be sandwiched between the outer layer and the one or more leaflets.
- sheet 512 defines a plane (i.e., the plane of the page).
- sheet 512 defines, in the plane, (i) panel 508 at a medial region of sheet 512, (ii) flaps 504, disposed peripherally to the panel, and (iii) first and second tab portions 526, also disposed peripherally from the panel.
- Each tab portion 526 includes outer layer 520o and inner layer 520i, and in the folded state, defines a respective leaflet-engaging tab 506.
- sheet 512 further defines bridging elements 522, via each of which a respective tab portion 526 is connected to panel 508.
- Flaps 504 are connected to panel 508 independently of the bridging elements.
- tab portions 526 flank panel 508 by being disposed, in the plane, on opposing lateral sides of the panel.
- panel 508, tab portions 526, and bridging elements 522 are arranged in a row that defines a lateral axis ax3 in the plane, axis ax3 passing through the panel, tab portions, and bridging elements.
- Axis ax3 typically passes between upstream flaps 504a and downstream flaps 504b.
- the fold axis ax2 of each flap 504 is disposed at an angle alpha_4 that is 30-60 degrees from lateral axis ax3.
- bridging elements 522 extend from respective edges of panel 508 and toward each other across first side 508a of the panel, and each of the leaflet-engaging tabs 506 protrudes from its respective bridging element away from the first side of the panel in the direction that the first side of the panel faces.
- FIGs. 12A-B and 13A-G are schematic illustrations of another connector 610 for connecting prosthetic leaflets (e.g., leaflets 58) to a frame of a prosthetic valve implant, in accordance with some applications of the invention.
- Connector 610 may be used with any of the implants described herein, or with a different prosthetic valve, mutatis mutandis.
- Connector 610 typically comprises a flexible sheet 612 that is folded to define elements of the connector. Further typically, sheet 612 is a single, unitary sheet (e.g., cut from a single piece of stock material, such as a fabric).
- Fig. 12A shows two perspective views of connector 610 (e.g., sheet 612 thereof) in its folded state, and Fig. 12B shows its unfolded state.
- Fig. 12B and 13A-G opposing sides of the sheet are differently shaded, e.g., as demonstrated by a corner of sheet 612 being curled over in Fig. 12B to show its reverse side.
- Connector 610 (e.g., in its folded state) is shaped to define a plurality of flaps 604, and a leaflet-receptacle 614 comprising one or more (e.g., two) leaflet-engaging tabs 606, such as a first leaflet-engaging tab 606a and a second leaflet-engaging tab 606b.
- Connector 610 is typically shaped to define a panel (e.g., a plate) 608. In the folded state, tabs 606 protrude from of a first side 608a of the panel, and each flap 604 folds over a second side 608b of the panel (e.g., a respective portion thereof).
- Flaps 604 are folded over or wrapped around elements of the frame of the prosthetic valve implant, e.g., as shown in Fig. 13G. Typically, flaps 604 are fixed in this disposition by stitches (not shown).
- connector 610 comprises four flaps 604, typically two upstream flaps 604a and two downstream flaps 604b.
- flaps 604 are arranged in a circuit such that each flap has two adjacent flaps around the circuit, and the fold axis ax4 of each flap is oriented at 60-120 degrees (e.g., 70-110 degrees, e.g., 80-100 degrees) from the fold axis of each of its adjacent flaps.
- the frame to which connector 610 is to be connected has a cellular structure with roughly diamond- shape cells, such an arrangement facilitates attachment of the connector to the frame, e.g., as shown in Fig. 13G.
- a connector comprising a flexible sheet (e.g., sheet 612) that is folded to define: (i) a panel (e.g., panel 608) that has a first side (e.g., side 608a), and a second side (e.g., side 608b) that is opposite the first side; (ii) a leaflet receptacle (e.g., receptacle 614), disposed on the first side of the panel, and protruding in a first direction away from the panel; and (iii) a plurality of flaps (e.g., flaps 604), each flap folded about a respective fold axis (e.g., axis ax4) such that at least part of each flap is disposed on the second side of the panel.
- a panel e.g., panel 608
- a leaflet receptacle e.g., receptacle 614
- flaps e.g., flaps 604
- Receptacle 614 is configured to sandwich one or more prosthetic leaflets between leaflet-engaging tabs 606a and 606b.
- stitching holes 616 are defined in leaflet- engaging tabs 606 to guide the introduction of stitches which will secure the leaflets sandwiched between the tabs.
- holes 616 are arranged into rows.
- each leaflet-engaging tab 606 may define a first row 618a of stitching holes and a second row 618b of stitching holes, the rows of one tab being aligned with the corresponding rows of the other tab.
- rows 618a and 618b diverge from each other at an angle alpha_5, typically such that that progressively downstream parts of the rows are progressively further from each other.
- angle alpha_5 may be 10-45 degrees (e.g., 10-30 degrees, e.g., 15-25 degrees, such as about 20 degrees).
- Downstream is defined by the direction in which the prosthetic leaflets facilitate one-way fluid flow, which itself is in part dependent on the orientation of the attachment of the leaflets to connectors 610.
- sheet 612 is folded such that each leaflet-engaging tab 606 comprises an outer layer 620o, and an inner layer 620i that is positioned to be sandwiched between the outer layer and the one or more leaflets.
- rows 618a and 618b are defined by inner layer 620i, and a third row 618c of stitching holes is defined by outer layer 620, and the folding of sheet 612 is such that row 618c aligns with row 618a.
- an angle alpha_7 between rows 618a and 618c i.e., at which rows 618a and 618c diverge from each other
- sheet 612 defines a plane (i.e., the plane of the page).
- sheet 612 defines, in the plane, (i) panel 608 (i.e., a panel portion of the sheet) at a medial region of sheet 612, (ii) flaps 604, disposed peripherally to the panel, and (iii) first and second tab portions 626, also disposed peripherally from the panel.
- Each tab portion 626 includes outer layer 620o and inner layer 620i, and in the folded state, defines a respective leaflet-engaging tab 606.
- Sheet 612 further defines bridging elements 622, via each of which a respective tab portion 626 is connected to panel 608. Flaps 604 are also connected to panel 608 via the bridging elements.
- each flap 604 is disposed on first side 608a of panel 608, and part of each flap is disposed on second side 608b.
- bridging elements 622 are typically disposed on first side 608a, and each flap 604 extends from one of the bridging elements and around panel 608 such that part of the flap is disposed on side 608a, and part is disposed on side 608b.
- tab portions 626 flank panel 608 (i.e., the panel portion of the sheet) by being disposed, in the plane, on opposing lateral sides of the panel.
- panel 608, tab portions 626, and bridging elements 622 are arranged in a row that defines a lateral axis ax5 in the plane, axis ax5 passing through the panel, tab portions, and bridging elements.
- Axis ax5 typically passes between upstream flaps 604a and downstream flaps 604b.
- the fold axis ax4 of each flap 604 is disposed at an angle alpha_6 that is 30-70 degrees from lateral axis ax5.
- Sheet 612 typically further defines a lapel 640 that, in the unfolded state, is lateral to each tab portion 626. Lapels 640 are described further hereinbelow.
- bridging elements 622 extend from respective edges of panel 608 and toward each other across first side 608a of the panel, and each of the leaflet-engaging tabs 606 protrudes from its respective bridging element away from the first side of the panel in the direction that the first side of the panel faces.
- Figs. 13A-G show steps in the folding of sheet 612 from the unfolded state to the folded state, in order to define connector 610, in accordance with some applications of the inventions.
- Folds are made in downstream regions of tab portions 626, e.g., the downstream edge of each layer 610o and/or each layer 610i is folded over to form respective folds 628 (Fig. 13A). This will provide each leaflet-engaging tab with a cushion 630, described hereinbelow.
- Folds 628 may be secured by stitching.
- Sheet 612 is folded in half along its longitudinal axis ax6 (or is simply bent around the longitudinal axis without creating a distinct fold), bringing tab portions 626 together (Fig. 13B).
- Commissural portions of two leaflets 58 are introduced, such that they are sandwiched together between portions 626. As shown, the positioning of the leaflets is typically such that they are disposed between the holes 616 of one portion 626, and those of the other portion 626. Holes 616 of row 618b of both portions 626 are stitched together by a first stitching 632. Stitching 632 therefore passes through leaflets 58a and 58b, thereby securing them to connector 610.
- tab portions 626 are folded, along a fold line 644, back against themselves, thereby defining inner layer 620i and outer layer 620o (Fig. 13C), and aligning rows 618c with rows 618a (e.g., such that the resulting angle between fold line 644 and row 618a is substantially equal to (e.g., within 5% of) the resulting angle between the fold line and row 168c).
- first stitching 632, and holes 616 of rows 618a and 618b are covered (e.g., hidden) by outer layer 620o.
- Rows 618c and 618a of one tab portion 626, leaflets 58a and 58b, and rows 618a and 618c of the other tab portion are then stitched together by a second stitching 634. This reinforces the connection of the leaflets to connector 610.
- tab portions 626 are formed into leaflet-engaging tabs 606.
- a method for use with a flexible sheet that, in an unfolded state of the sheet, defines a panel (e.g., panel 608) at a medial region of the sheet, a first tab portion disposed peripherally to the panel, and a second tab portion disposed peripherally to the panel opposite the first tab portion, the method comprising:
- first tab portion sandwiching, between the first tab portion and the second tab portion, (i) a first commissural portion of a first prosthetic leaflet, and (ii) a second commissural portion of a second prosthetic leaflet;
- first stitching e.g., stitching 632
- first stitching e.g., stitching 632
- first tab portion back against itself to form the first tab portion into a first tab having first-tab outer layer and a first-tab inner layer, such that the first-tab inner layer is sandwiched between the first-tab outer layer and the first commissural portion, and
- fold line 644 is closer to first stitching 632 than to second stitching 634.
- an angle alpha_8 between fold line 644 and first stitching 632 (Fig. 13B) is smaller than an angle alpha_9 between the fold line and second stitching 634 (Fig. 13C).
- Angle alpha_8 is also the angle between fold line 644 and row 618b.
- Angle alpha_9 is also the angle between fold line 644 and row 618c (and also typically between the fold line and row 618a).
- the folding of tab portion 626 back against itself comprises folding the tab portion such that an angle between the fold line and row 618b is smaller than both (i) the angle between the fold line and row 618a, and (ii) the angle between the fold line and row 618c.
- a unitary flexible sheet e.g., sheet 612
- a panel e.g., panel 608, having a first side facing in a first direction, and a second side that is opposite the first side;
- a first tab e.g., leaflet-engaging tab 606a
- a first tab disposed on the first side of the panel, having a first-tab outer layer and a first-tab inner layer, and protruding in the first direction away from the panel;
- a second tab e.g., leaflet-engaging tab 606a
- a second tab disposed on the first side of the panel, having a second-tab outer layer and a second-tab inner layer, and protruding in the first direction away from the panel;
- first prosthetic leaflet having a first-leaflet commissural portion disposed between the first-tab inner layer and the second-tab inner layer;
- a second prosthetic leaflet having a second-leaflet commissural portion disposed between the first-tab inner layer and the second-tab inner layer;
- a first stitching (e.g., stitching 632), stitched through the first-tab inner layer, the first-leaflet commissural portion, the second-leaflet commissural portion, and the second-tab inner layer;
- a second stitching (e.g., stitching 634), stitched through the first-tab outer layer, the first-tab inner layer, the first-leaflet commissural portion, the second-leaflet commissural portion, the second-tab inner layer, and the second-tab outer layer, wherein the first-tab outer layer and the second-tab outer layer cover the first stitching.
- each leaflet 58 e.g., unstitched parts of the commissural portion of each leaflet
- regions of each leaflet 58 e.g., unstitched parts of the commissural portion of each leaflet
- regions of each leaflet 58 e.g., unstitched parts of the commissural portion of each leaflet
- bridging elements 622 e.g., sandwiched
- the unstitched part of the commissural portion of one leaflet is moved away from the unstitched part of the commissural portion of the other leaflet.
- the step shown in Fig. 13C brings lapels 640 into contact with bridging elements 622.
- the step shown in Fig. 13D typically causes each bridging element 622 to move with the bridging element 622 with which it is in contact, and folding with respect to outer layer 620i of leaflet-engaging tabs 606.
- stitches are passed through lapel 640, bridging element 622, leaflet 58, and panel 608. This stitching may be an independent step, or may be achieved when securing flaps 604 to the frame of the prosthetic valve, e.g., as described hereinbelow.
- Fig. 13E shows perspective views of the state shown in Fig. 13D.
- Each leaflet 58 has a downstream edge 638.
- leaflet-engaging tabs 606 typically extend in a downstream direction beyond downstream edges 638.
- cushions 630 are typically positioned such that at least part of each cushion is disposed further downstream than downstream edges 638. Tabs 606 and/or cushions 630 are thereby configured to inhibit movement of the commissural portion of each leaflet 58 (and especially of downstream edges 638) toward the frame of the prosthetic valve. It is hypothesized by the inventors that this reduces a likelihood of leaflets 58 becoming damaged over time due to contact with the frame.
- a unitary flexible sheet folded to define (i) a panel, defining a plane, and having a first side facing in a first direction away from the plane, and a second side that is opposite the first side; (ii) a first tab, disposed on the first side of the panel, and protruding in the first direction away from the panel; and (iii) a second tab, disposed on the first side of the panel, and protruding in the first direction away from the panel;
- the sheet is folded to define a first cushion at a downstream edge of the first tab, the first cushion being configured and positioned to inhibit deflection of a downstream portion of the first prosthetic leaflet away from the second prosthetic leaflet and toward the plane
- the sheet is folded to define a second cushion at a downstream edge of the second tab, the second cushion being configured and positioned to inhibit deflection of a downstream portion of the second prosthetic leaflet away from the first prosthetic leaflet and toward the plane.
- each cushion 630 is typically formed by folding at least one fold 628. Therefore, for some applications, sheet 612 defines a first- tab fold (in the first tab) and a second-tab fold (in the second tab), the first cushion comprises the first-tab fold, folded between the first-tab inner layer and the first-tab outer layer, and the second cushion comprises the second-tab fold, folded between the second-tab inner layer and the second-tab outer layer.
- each cushion is formed by folding a fold in each of the layers of each leaflet-engaging tab. That is, for some applications:
- the first-tab fold described in the previous paragraph is a first-tab outer fold, continuous with the first-tab outer layer
- the second-tab fold described in the previous paragraph is a second-tab outer fold, continuous with the second-tab outer layer
- the sheet further defines:
- the first cushion comprises:
- the second cushion comprises:
- each leaflet-engaging tab 606 defines a downstream opening 642 between inner layer 620i and outer layer 620o.
- three connectors 610 are used to connect three leaflets 58 at three commissures, to form a valvular assembly 650 that comprises tri-leaflet check-valve (Fig. 13F).
- valvular assembly connectors 610 are arranged circumferentially, and leaflets 58 extend radially inward from the connectors.
- Each connector 610 is secured to the frame of the prosthetic valve (Fig. 13G).
- valvular assembly 650 may be disposed within lumen 38, and connectors 610 may be secured to frame 30 at tubular portion 32, and/or to frame 60 (e.g., at ring 66). Flaps 604 are folded over components of the frame of the prosthetic valve (which are shown in phantom), and secured by stitching. For some applications, some of this stitching may pass through several elements, such as flaps 604, panel 608, leaflets 58, bridging elements 622, and/or lapels 640. Typically, but not necessarily, valvular assembly 650 is assembled before connectors 610 are secured to the frame of the prosthetic valve.
- Valvular assembly 650 is configured such that, when secured to the frame of the prosthetic valve, the valvular assembly facilitates upstream-to-downstream fluid flow through the lumen of the prosthetic valve by the three prosthetic leaflets opening (i.e., the downstream edges of the leaflets move away from each other), and to inhibit downstream- to-upstream fluid flow through the lumen by the three prosthetic leaflets closing (i.e., the downstream edges of the leaflets move toward each other).
- the valvular assembly facilitates upstream-to-downstream fluid flow through the lumen of the prosthetic valve by the three prosthetic leaflets opening (i.e., the downstream edges of the leaflets move away from each other), and to inhibit downstream- to-upstream fluid flow through the lumen by the three prosthetic leaflets closing (i.e., the downstream edges of the leaflets move toward each other).
- Figs. 13A-G show a particular sequence, and although some of the steps are necessarily performed before others, it is to be understood that some of the steps may be performed in a different order to that shown. For example, folds 628 may be folded at a later stage to that shown.
- FIGs. 12A- 13G It is to be noted that each tab 606 defines a loose region 646, further away from panel 608 than both stitching 634 and stitching 632. Loose region 646 is relatively loose with respect to leaflets 58. When the valvular assembly is coupled to a tubular frame as described hereinabove, loose region 646 is disposed radially inward from first stitching 632 and second stitching 634. Reference is now made to Figs.
- connector 710 for connecting prosthetic leaflets (e.g., leaflets 58) to a frame of a prosthetic valve implant, in accordance with some applications of the invention.
- Connector 710 may be used with any of the implants described herein, or with a different prosthetic valve, mutatis mutandis.
- connector 710 is identical to connector 610, except that it further comprises a separate flexible sheet 712, used in combination with sheet 612.
- sheet 712 is placed between the commissural portions of the leaflets 58 being connected, such that when the commissural portions of the leaflets are sandwiched between tab portions 626, sheet 712 is sandwiched between the commissural portions of the leaflets.
- Fig. 14A is analogous to Fig. 13B, but showing the addition of separate flexible sheet 712.
- Fig. 14B is analogous to the left-side image of Fig. 13E, but showing the addition of separate flexible sheet 712.
- the positioning of sheet 712 is typically such that it is disposed between holes 616 of row 618b of one tab portion 626, and the holes of row 618a of the other tab portion.
- the positioning of sheet 712 is also typically such that it is disposed between holes 616 of row 618a of one tab portion 626, and the holes of row 618a of the other tab portion. Therefore, for applications in which sheet 712 is used, first stitching 632 is typically stitched through sheet 712, and second stitching 634 is also typically stitched through sheet 712.
- sheet 712 protrudes in a downstream direction beyond tabs 606 (e.g., beyond cushions 630).
- sheet 712 results in the commissural portion of each leaflet being sandwiched between two layers of fabric, rather than between a layer of fabric and the other leaflet. It is hypothesized by the inventors that this strengthens the connection between the leaflets and the connector, and reduces a likelihood of tearing of the leaflets where they are stitched to the connector.
- a biocompatible adhesive (e.g., comprising a polymer adhesive and/or a collagen adhesive) may be used to reinforce stitching of the implant.
- the adhesive is applied at (e.g., onto) stitching that secures the leaflets to fabric, such as stitching between the leaflets and the covering that lines the tubular portion of the implant (e.g., the adhesive being applied along the arched stitch line that follows the arch of each leaflet), and/or stitching between the leaflets and the commissural connectors (e.g., the adhesive being applied along one or more rows of holes of the connector's tab portions, and/or to the stitching that passes through the holes).
- the adhesive is applied at (e.g., onto) stitching that secures fabric to fabric, such as stitching between different parts of covering 23, and/or stitching that secures the flaps of a connector. It is hypothesized by the inventors that such use of an adhesive reduces a likelihood of the stitching cutting through the prosthetic leaflet or the fabric.
- a prosthetic valve from two (e.g., concentric) frames
- the ability to divide the frame elements required between the two frames in a manner that would not be possible in a single frame, or in a manner that, if a single frame were used, would increase the size (e.g., the diameter or the length) of the implant in its compressed state.
- the use of two frames allows different sizes of the implant to be compressed ("crimped") to the same or similar diameter, and for some such applications, to be delivered using the same delivery tool (e.g., delivery tool 89).
- an implant of a larger size may have a lumen diameter that is at least 15 percent greater than the lumen diameter of an implant of a smaller size (in their respective expanded states), but in their compressed states, the diameter of the implant of the larger size may be no more than 2 percent greater than the diameter of the implant of the smaller size.
- a delivery tool is provided for use with different sizes of the implant, e.g., with the implants provided separately.
- a kit is provided containing a delivery tool and implants of different sizes.
- radially outward means portions of the element are disposed progressively further outward from a central point (such as longitudinal axis axl or tubular portion 32), but does not necessarily mean disposed at 90 degrees with respect to longitudinal axis axl.
- flanges 54 may extend radially outward at 90 degrees with respect to longitudinal axis axl, but may alternatively extend radially outward at a shallower angle with respect to the longitudinal axis.
Landscapes
- Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Cardiology (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Transplantation (AREA)
- Heart & Thoracic Surgery (AREA)
- Vascular Medicine (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Manufacturing & Machinery (AREA)
- Mechanical Engineering (AREA)
- Prostheses (AREA)
Applications Claiming Priority (5)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US201662372861P | 2016-08-10 | 2016-08-10 | |
PCT/IL2017/050873 WO2018029680A1 (en) | 2016-08-10 | 2017-08-08 | Prosthetic valve with concentric frames |
US15/878,206 US9987132B1 (en) | 2016-08-10 | 2018-01-23 | Prosthetic valve with leaflet connectors |
US15/995,597 US10098732B1 (en) | 2016-08-10 | 2018-06-01 | Prosthetic valve with leaflet connectors |
PCT/IL2018/050869 WO2019030753A1 (en) | 2016-08-10 | 2018-08-07 | PROSTHETIC VALVE WITH SHEET CONNECTORS |
Publications (1)
Publication Number | Publication Date |
---|---|
EP3664748A1 true EP3664748A1 (de) | 2020-06-17 |
Family
ID=59626647
Family Applications (3)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP21157988.3A Pending EP3848003A1 (de) | 2016-08-10 | 2017-08-08 | Klappenprothese mit konzentrischen rahmen |
EP17752184.6A Active EP3496664B1 (de) | 2016-08-10 | 2017-08-08 | Klappenprothese mit konzentrischen rahmen |
EP18752635.5A Pending EP3664748A1 (de) | 2016-08-10 | 2018-08-07 | Herzklappenprothese mit segelkonnektoren |
Family Applications Before (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP21157988.3A Pending EP3848003A1 (de) | 2016-08-10 | 2017-08-08 | Klappenprothese mit konzentrischen rahmen |
EP17752184.6A Active EP3496664B1 (de) | 2016-08-10 | 2017-08-08 | Klappenprothese mit konzentrischen rahmen |
Country Status (5)
Country | Link |
---|---|
US (6) | US10856975B2 (de) |
EP (3) | EP3848003A1 (de) |
CN (4) | CN114587712A (de) |
CA (2) | CA3031187A1 (de) |
WO (2) | WO2018029680A1 (de) |
Families Citing this family (67)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8870950B2 (en) | 2009-12-08 | 2014-10-28 | Mitral Tech Ltd. | Rotation-based anchoring of an implant |
US20110224785A1 (en) | 2010-03-10 | 2011-09-15 | Hacohen Gil | Prosthetic mitral valve with tissue anchors |
US8579964B2 (en) | 2010-05-05 | 2013-11-12 | Neovasc Inc. | Transcatheter mitral valve prosthesis |
US11653910B2 (en) | 2010-07-21 | 2023-05-23 | Cardiovalve Ltd. | Helical anchor implantation |
US9763657B2 (en) | 2010-07-21 | 2017-09-19 | Mitraltech Ltd. | Techniques for percutaneous mitral valve replacement and sealing |
WO2012087842A1 (en) | 2010-12-23 | 2012-06-28 | The Foundry, Llc | System for mitral valve repair and replacement |
US9554897B2 (en) | 2011-04-28 | 2017-01-31 | Neovasc Tiara Inc. | Methods and apparatus for engaging a valve prosthesis with tissue |
US9308087B2 (en) | 2011-04-28 | 2016-04-12 | Neovasc Tiara Inc. | Sequentially deployed transcatheter mitral valve prosthesis |
EP3417813B1 (de) | 2011-08-05 | 2020-05-13 | Cardiovalve Ltd | Perkutaner mitralklappenersatz |
WO2013021374A2 (en) | 2011-08-05 | 2013-02-14 | Mitraltech Ltd. | Techniques for percutaneous mitral valve replacement and sealing |
US8852272B2 (en) | 2011-08-05 | 2014-10-07 | Mitraltech Ltd. | Techniques for percutaneous mitral valve replacement and sealing |
US9345573B2 (en) | 2012-05-30 | 2016-05-24 | Neovasc Tiara Inc. | Methods and apparatus for loading a prosthesis onto a delivery system |
US8628571B1 (en) | 2012-11-13 | 2014-01-14 | Mitraltech Ltd. | Percutaneously-deliverable mechanical valve |
US9968443B2 (en) | 2012-12-19 | 2018-05-15 | W. L. Gore & Associates, Inc. | Vertical coaptation zone in a planar portion of prosthetic heart valve leaflet |
ES2934670T3 (es) | 2013-01-24 | 2023-02-23 | Cardiovalve Ltd | Válvulas protésicas ancladas de forma ventricular |
US9572665B2 (en) | 2013-04-04 | 2017-02-21 | Neovasc Tiara Inc. | Methods and apparatus for delivering a prosthetic valve to a beating heart |
CN108294846A (zh) | 2013-05-20 | 2018-07-20 | 托尔福公司 | 可植入心脏瓣膜装置、二尖瓣修复装置以及相关系统和方法 |
EP3122289A1 (de) * | 2014-03-26 | 2017-02-01 | St. Jude Medical, Cardiology Division, Inc. | Rahmen für transkatheter-mitralklappenstent |
WO2016016899A1 (en) | 2014-07-30 | 2016-02-04 | Mitraltech Ltd. | Articulatable prosthetic valve |
US10507101B2 (en) * | 2014-10-13 | 2019-12-17 | W. L. Gore & Associates, Inc. | Valved conduit |
WO2016125160A1 (en) | 2015-02-05 | 2016-08-11 | Mitraltech Ltd. | Prosthetic valve with axially-sliding frames |
US9974651B2 (en) | 2015-02-05 | 2018-05-22 | Mitral Tech Ltd. | Prosthetic valve with axially-sliding frames |
US9962260B2 (en) * | 2015-03-24 | 2018-05-08 | St. Jude Medical, Cardiology Division, Inc. | Prosthetic mitral valve |
CN111658234B (zh) | 2015-08-21 | 2023-03-10 | 托尔福公司 | 可植入心脏瓣膜装置、二尖瓣修复装置以及相关系统和方法 |
US10350066B2 (en) | 2015-08-28 | 2019-07-16 | Edwards Lifesciences Cardiaq Llc | Steerable delivery system for replacement mitral valve and methods of use |
CA3006010C (en) * | 2015-12-28 | 2023-09-26 | Tendyne Holdings, Inc. | Atrial pocket closures for prosthetic heart valves |
EP4183372A1 (de) | 2016-01-29 | 2023-05-24 | Neovasc Tiara Inc. | Klappenprothese zur vermeidung von abflussverstopfung |
US10531866B2 (en) | 2016-02-16 | 2020-01-14 | Cardiovalve Ltd. | Techniques for providing a replacement valve and transseptal communication |
US10350062B2 (en) | 2016-07-21 | 2019-07-16 | Edwards Lifesciences Corporation | Replacement heart valve prosthesis |
GB201613219D0 (en) | 2016-08-01 | 2016-09-14 | Mitraltech Ltd | Minimally-invasive delivery systems |
WO2018029680A1 (en) | 2016-08-10 | 2018-02-15 | Mitraltech Ltd. | Prosthetic valve with concentric frames |
US10441421B2 (en) * | 2016-10-28 | 2019-10-15 | St. Jude Medical, Cardiology Division, Inc. | Prosthetic mitral valve |
CA3042588A1 (en) | 2016-11-21 | 2018-05-24 | Neovasc Tiara Inc. | Methods and systems for rapid retraction of a transcatheter heart valve delivery system |
US10702378B2 (en) | 2017-04-18 | 2020-07-07 | Twelve, Inc. | Prosthetic heart valve device and associated systems and methods |
US10433961B2 (en) | 2017-04-18 | 2019-10-08 | Twelve, Inc. | Delivery systems with tethers for prosthetic heart valve devices and associated methods |
US10792151B2 (en) | 2017-05-11 | 2020-10-06 | Twelve, Inc. | Delivery systems for delivering prosthetic heart valve devices and associated methods |
US10709591B2 (en) | 2017-06-06 | 2020-07-14 | Twelve, Inc. | Crimping device and method for loading stents and prosthetic heart valves |
US10786352B2 (en) | 2017-07-06 | 2020-09-29 | Twelve, Inc. | Prosthetic heart valve devices and associated systems and methods |
US10729541B2 (en) | 2017-07-06 | 2020-08-04 | Twelve, Inc. | Prosthetic heart valve devices and associated systems and methods |
US11246704B2 (en) | 2017-08-03 | 2022-02-15 | Cardiovalve Ltd. | Prosthetic heart valve |
US11793633B2 (en) | 2017-08-03 | 2023-10-24 | Cardiovalve Ltd. | Prosthetic heart valve |
EP3661457A1 (de) | 2017-08-03 | 2020-06-10 | Cardiovalve Ltd | Herzklappenprothese |
US10537426B2 (en) | 2017-08-03 | 2020-01-21 | Cardiovalve Ltd. | Prosthetic heart valve |
US10575948B2 (en) | 2017-08-03 | 2020-03-03 | Cardiovalve Ltd. | Prosthetic heart valve |
US10888421B2 (en) | 2017-09-19 | 2021-01-12 | Cardiovalve Ltd. | Prosthetic heart valve with pouch |
CN111263622A (zh) | 2017-08-25 | 2020-06-09 | 内奥瓦斯克迪亚拉公司 | 顺序展开的经导管二尖瓣假体 |
US10881511B2 (en) | 2017-09-19 | 2021-01-05 | Cardiovalve Ltd. | Prosthetic valve with tissue anchors configured to exert opposing clamping forces on native valve tissue |
US9895226B1 (en) | 2017-10-19 | 2018-02-20 | Mitral Tech Ltd. | Techniques for use with prosthetic valve leaflets |
GB201720803D0 (en) | 2017-12-13 | 2018-01-24 | Mitraltech Ltd | Prosthetic Valve and delivery tool therefor |
GB201800399D0 (en) | 2018-01-10 | 2018-02-21 | Mitraltech Ltd | Temperature-control during crimping of an implant |
EP3720390B1 (de) | 2018-01-25 | 2024-05-01 | Edwards Lifesciences Corporation | Einführsystem zur unterstützten rückgewinnung oder neupositionierung eines klappenersatzes nach dem einsetzen |
CA3096002A1 (en) | 2018-04-19 | 2019-10-24 | Cardiovalve Ltd. | Prosthetic heart valve with pouch |
US11083571B2 (en) * | 2018-06-27 | 2021-08-10 | Edwards Lifesciences Corporation | Frame for prosthetic heart valve |
GB2577052B (en) * | 2018-09-11 | 2021-04-28 | Strait Access Tech Holdings Pty Ltd | Expandable sleeved stent and method of making such stent |
US10779946B2 (en) | 2018-09-17 | 2020-09-22 | Cardiovalve Ltd. | Leaflet-testing apparatus |
CA3118599A1 (en) | 2018-11-08 | 2020-05-14 | Neovasc Tiara Inc. | Ventricular deployment of a transcatheter mitral valve prosthesis |
CA3134940A1 (en) | 2019-03-25 | 2020-10-01 | Inqb8 Medical Technologies Llc | Prosthetic heart valve |
CN113811265A (zh) | 2019-04-01 | 2021-12-17 | 内奥瓦斯克迪亚拉公司 | 能够以可控的方式部署的假体瓣膜 |
CA3136334A1 (en) | 2019-04-10 | 2020-10-15 | Neovasc Tiara Inc. | Prosthetic valve with natural blood flow |
WO2020236931A1 (en) | 2019-05-20 | 2020-11-26 | Neovasc Tiara Inc. | Introducer with hemostasis mechanism |
CN114144144A (zh) | 2019-06-20 | 2022-03-04 | 内奥瓦斯克迪亚拉公司 | 低轮廓假体二尖瓣 |
EP3811904A4 (de) * | 2019-07-29 | 2022-04-13 | Miyamoto, Shinka | Matrize zur formung einer künstlichen herzklappe und künstliche herzklappe |
US20230059371A1 (en) | 2020-02-04 | 2023-02-23 | Cardiovalve Ltd. | Support-guided steering of a catheter |
CA3193420A1 (en) * | 2020-08-28 | 2022-03-03 | inQB8 Medical Technologies, LLC | Prosthetic heart valve |
WO2022057799A1 (en) * | 2020-09-15 | 2022-03-24 | Hangzhou Valgen Medtech Co., Ltd. | Artificial Heart Valve Stent, Artificial Heart Valve and Artificial Heart Valve Replacement System |
US11660194B1 (en) * | 2022-06-20 | 2023-05-30 | University Of Utah Research Foundation | Cartilage and bone harvest and delivery system and methods |
US11931256B1 (en) * | 2023-09-19 | 2024-03-19 | Seven Summits Medical, Inc. | Expandable prosthetic heart valve |
Family Cites Families (1334)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
NL143127B (nl) | 1969-02-04 | 1974-09-16 | Rhone Poulenc Sa | Versterkingsorgaan voor een defecte hartklep. |
US3604488A (en) | 1969-11-19 | 1971-09-14 | Vermont American Corp | Screwdriver attachment |
US3840018A (en) | 1973-01-31 | 1974-10-08 | M Heifetz | Clamp for occluding tubular conduits in the human body |
US3874388A (en) | 1973-02-12 | 1975-04-01 | Ochsner Med Found Alton | Shunt defect closure system |
US3898701A (en) | 1974-01-17 | 1975-08-12 | Russa Joseph | Implantable heart valve |
US4340091A (en) | 1975-05-07 | 1982-07-20 | Albany International Corp. | Elastomeric sheet materials for heart valve and other prosthetic implants |
US4042979A (en) | 1976-07-12 | 1977-08-23 | Angell William W | Valvuloplasty ring and prosthetic method |
US4118805A (en) | 1977-02-28 | 1978-10-10 | Codman & Shurtleff, Inc. | Artificial sphincter |
ES474582A1 (es) | 1978-10-26 | 1979-11-01 | Aranguren Duo Iker | Procedimiento para la instalacion de valvulas mitrales en sulugar anatomico, mediante anclaje de cordajes en pilar arti-ficial |
US4214349A (en) | 1978-11-30 | 1980-07-29 | Midland-Ross Corporation | Tie wrap |
US4222126A (en) | 1978-12-14 | 1980-09-16 | The United States Of America As Represented By The Secretary Of The Department Of Health, Education & Welfare | Unitized three leaflet heart valve |
US4275469A (en) | 1979-12-13 | 1981-06-30 | Shelhigh Inc. | Prosthetic heart valve |
GB2084468B (en) | 1980-09-25 | 1984-06-06 | South African Inventions | Surgical implant |
US4473928A (en) | 1980-11-20 | 1984-10-02 | Tridon Limited | Hose clamps |
IT1144379B (it) | 1981-07-14 | 1986-10-29 | Sorin Biomedica Spa | Protesi valvolare cardiaca |
DE3230858C2 (de) | 1982-08-19 | 1985-01-24 | Ahmadi, Ali, Dr. med., 7809 Denzlingen | Ringprothese |
US4892541A (en) | 1982-11-29 | 1990-01-09 | Tascon Medical Technology Corporation | Heart valve prosthesis |
US4434828A (en) | 1982-12-20 | 1984-03-06 | Richard Trincia | Screwdriver with handle for storing bits |
JPS6137235A (ja) | 1984-07-31 | 1986-02-22 | テルモ株式会社 | 人工弁 |
US4625727A (en) | 1985-01-24 | 1986-12-02 | Leiboff Arnold R | Anastomosis device with excisable frame |
US4712549A (en) | 1985-07-01 | 1987-12-15 | Edward Weck & Co. | Automatic hemostatic clip applier |
US4853986A (en) | 1986-01-02 | 1989-08-08 | The Awareness Marketing Corporation | Water level control |
CA1303298C (en) | 1986-08-06 | 1992-06-16 | Alain Carpentier | Flexible cardiac valvular support prosthesis |
US4961738A (en) | 1987-01-28 | 1990-10-09 | Mackin Robert A | Angioplasty catheter with illumination and visualization within angioplasty balloon |
US4972494A (en) | 1988-02-26 | 1990-11-20 | R. J. Reynolds Tobacco Company | Package inspection system |
US4917698A (en) | 1988-12-22 | 1990-04-17 | Baxter International Inc. | Multi-segmented annuloplasty ring prosthesis |
CH678393A5 (de) | 1989-01-26 | 1991-09-13 | Ulrich Prof Dr Med Sigwart | |
WO1990009153A1 (en) | 1989-02-13 | 1990-08-23 | Baxter International Inc. | Selectively flexible annuloplasty ring |
US4994077A (en) | 1989-04-21 | 1991-02-19 | Dobben Richard L | Artificial heart valve for implantation in a blood vessel |
US5314473A (en) | 1989-07-20 | 1994-05-24 | Godin Norman J | Prosthesis for preventing gastric reflux into the esophagus |
US5290300A (en) | 1989-07-31 | 1994-03-01 | Baxter International Inc. | Flexible suture guide and holder |
US5632746A (en) | 1989-08-16 | 1997-05-27 | Medtronic, Inc. | Device or apparatus for manipulating matter |
US5078739A (en) | 1990-07-20 | 1992-01-07 | Janus Biomedical, Inc. | Bileaflet heart valve with external leaflets |
US5626609A (en) | 1990-10-05 | 1997-05-06 | United States Surgical Corporation | Endoscopic surgical instrument |
US5108420A (en) | 1991-02-01 | 1992-04-28 | Temple University | Aperture occlusion device |
US5329923A (en) | 1991-02-15 | 1994-07-19 | Lundquist Ingemar H | Torquable catheter |
US5397351A (en) | 1991-05-13 | 1995-03-14 | Pavcnik; Dusan | Prosthetic valve for percutaneous insertion |
ATE182062T1 (de) | 1991-11-29 | 1999-07-15 | Cook William Europ | Verschlussprothese für die katheterplazierung |
US5201880A (en) | 1992-01-27 | 1993-04-13 | Pioneering Technologies, Inc. | Mitral and tricuspid annuloplasty rings |
US5306296A (en) | 1992-08-21 | 1994-04-26 | Medtronic, Inc. | Annuloplasty and suture rings |
WO1993015690A2 (en) | 1992-01-27 | 1993-08-19 | Medtronic, Inc. | Annuloplasty and suture rings |
FR2688401B1 (fr) | 1992-03-12 | 1998-02-27 | Thierry Richard | Endoprothese expansible pour organe tubulaire humain ou animal, et outil de mise en place. |
US5201757A (en) | 1992-04-03 | 1993-04-13 | Schneider (Usa) Inc. | Medial region deployment of radially self-expanding stents |
US5332402A (en) | 1992-05-12 | 1994-07-26 | Teitelbaum George P | Percutaneously-inserted cardiac valve |
US5405378A (en) | 1992-05-20 | 1995-04-11 | Strecker; Ernst P. | Device with a prosthesis implantable in the body of a patient |
US5325845A (en) | 1992-06-08 | 1994-07-05 | Adair Edwin Lloyd | Steerable sheath for use with selected removable optical catheter |
US5258008A (en) | 1992-07-29 | 1993-11-02 | Wilk Peter J | Surgical stapling device and associated method |
US5300034A (en) | 1992-07-29 | 1994-04-05 | Minnesota Mining And Manufacturing Company | Iv injection site for the reception of a blunt cannula |
US6074417A (en) | 1992-11-16 | 2000-06-13 | St. Jude Medical, Inc. | Total mitral heterologous bioprosthesis to be used in mitral or tricuspid heart replacement |
US6283127B1 (en) | 1992-12-03 | 2001-09-04 | Wesley D. Sterman | Devices and methods for intracardiac procedures |
US6346074B1 (en) | 1993-02-22 | 2002-02-12 | Heartport, Inc. | Devices for less invasive intracardiac interventions |
US6125852A (en) | 1993-02-22 | 2000-10-03 | Heartport, Inc. | Minimally-invasive devices and methods for treatment of congestive heart failure |
US5972030A (en) | 1993-02-22 | 1999-10-26 | Heartport, Inc. | Less-invasive devices and methods for treatment of cardiac valves |
US6010531A (en) | 1993-02-22 | 2000-01-04 | Heartport, Inc. | Less-invasive devices and methods for cardiac valve surgery |
US5797960A (en) | 1993-02-22 | 1998-08-25 | Stevens; John H. | Method and apparatus for thoracoscopic intracardiac procedures |
US5374286A (en) | 1993-03-31 | 1994-12-20 | Medtronic, Inc. | Torque indicator for fixed screw leads |
US5715817A (en) | 1993-06-29 | 1998-02-10 | C.R. Bard, Inc. | Bidirectional steering catheter |
US5450860A (en) | 1993-08-31 | 1995-09-19 | W. L. Gore & Associates, Inc. | Device for tissue repair and method for employing same |
US5651785A (en) | 1993-09-20 | 1997-07-29 | Abela Laser Systems, Inc. | Optical fiber catheter and method |
US5713950A (en) | 1993-11-01 | 1998-02-03 | Cox; James L. | Method of replacing heart valves using flexible tubes |
US5607444A (en) | 1993-12-02 | 1997-03-04 | Advanced Cardiovascular Systems, Inc. | Ostial stent for bifurcations |
AU1011595A (en) | 1994-01-13 | 1995-07-20 | Ethicon Inc. | Spiral surgical tack |
US5843120A (en) | 1994-03-17 | 1998-12-01 | Medinol Ltd. | Flexible-expandable stent |
US6165210A (en) | 1994-04-01 | 2000-12-26 | Gore Enterprise Holdings, Inc. | Self-expandable helical intravascular stent and stent-graft |
US5824041A (en) | 1994-06-08 | 1998-10-20 | Medtronic, Inc. | Apparatus and methods for placement and repositioning of intraluminal prostheses |
US6217610B1 (en) | 1994-07-29 | 2001-04-17 | Edwards Lifesciences Corporation | Expandable annuloplasty ring |
US5582616A (en) | 1994-08-05 | 1996-12-10 | Origin Medsystems, Inc. | Surgical helical fastener with applicator |
US5593424A (en) | 1994-08-10 | 1997-01-14 | Segmed, Inc. | Apparatus and method for reducing and stabilizing the circumference of a vascular structure |
US6015429A (en) | 1994-09-08 | 2000-01-18 | Gore Enterprise Holdings, Inc. | Procedures for introducing stents and stent-grafts |
US5765682A (en) | 1994-10-13 | 1998-06-16 | Menlo Care, Inc. | Restrictive package for expandable or shape memory medical devices and method of preventing premature change of same |
US5647857A (en) | 1995-03-16 | 1997-07-15 | Endotex Interventional Systems, Inc. | Protective intraluminal sheath |
US5607470A (en) | 1995-05-01 | 1997-03-04 | Milo; Simcha | Suture rings for prosthetic heart valves |
US5716417A (en) | 1995-06-07 | 1998-02-10 | St. Jude Medical, Inc. | Integral supporting structure for bioprosthetic heart valve |
US6010530A (en) | 1995-06-07 | 2000-01-04 | Boston Scientific Technology, Inc. | Self-expanding endoluminal prosthesis |
US5814098A (en) | 1995-06-07 | 1998-09-29 | St. Jude Medical, Inc. | Adjustable sizing apparatus |
US5676653A (en) | 1995-06-27 | 1997-10-14 | Arrow International Investment Corp. | Kink-resistant steerable catheter assembly |
US5713948A (en) | 1995-07-19 | 1998-02-03 | Uflacker; Renan | Adjustable and retrievable graft and graft delivery system for stent-graft system |
US5662683A (en) | 1995-08-22 | 1997-09-02 | Ortho Helix Limited | Open helical organic tissue anchor and method of facilitating healing |
US6193745B1 (en) | 1995-10-03 | 2001-02-27 | Medtronic, Inc. | Modular intraluminal prosteheses construction and methods |
US5749371A (en) | 1995-10-06 | 1998-05-12 | Zadini; Filiberto P. | Automatic guidewire placement device for medical catheters |
AU720907B2 (en) | 1995-12-01 | 2000-06-15 | Medtronic, Inc. | Annuloplasty prosthesis |
US5730150A (en) | 1996-01-16 | 1998-03-24 | B. Braun Medical Inc. | Guidewire dispenser |
EP0932426A4 (de) | 1996-02-02 | 2003-07-30 | Transvascular Inc | Verfahren und vorrichtung zum verbinden von in benachbarten blutgefässen oder in anderen anatomischen strukturen angebrachten öffnungen |
US5957953A (en) | 1996-02-16 | 1999-09-28 | Smith & Nephew, Inc. | Expandable suture anchor |
US5702397A (en) | 1996-02-20 | 1997-12-30 | Medicinelodge, Inc. | Ligament bone anchor and method for its use |
US5716370A (en) | 1996-02-23 | 1998-02-10 | Williamson, Iv; Warren | Means for replacing a heart valve in a minimally invasive manner |
US6402780B2 (en) | 1996-02-23 | 2002-06-11 | Cardiovascular Technologies, L.L.C. | Means and method of replacing a heart valve in a minimally invasive manner |
US6132390A (en) | 1996-02-28 | 2000-10-17 | Eupalamus Llc | Handle for manipulation of a stylet used for deflecting a tip of a lead or catheter |
US6702846B2 (en) | 1996-04-09 | 2004-03-09 | Endocare, Inc. | Urological stent therapy system and method |
US5885228A (en) | 1996-05-08 | 1999-03-23 | Heartport, Inc. | Valve sizer and method of use |
US6007544A (en) | 1996-06-14 | 1999-12-28 | Beth Israel Deaconess Medical Center | Catheter apparatus having an improved shape-memory alloy cuff and inflatable on-demand balloon for creating a bypass graft in-vivo |
US5776140A (en) | 1996-07-16 | 1998-07-07 | Cordis Corporation | Stent delivery system |
US6569188B2 (en) | 1996-08-05 | 2003-05-27 | Arthrex, Inc. | Hex drive bioabsorbable tissue anchor |
US5669919A (en) | 1996-08-16 | 1997-09-23 | Medtronic, Inc. | Annuloplasty system |
US6464595B2 (en) | 1996-08-23 | 2002-10-15 | Telesystems Co., Ltd. | Automatic bowling scoring apparatus and bowling alley management system |
US5741297A (en) | 1996-08-28 | 1998-04-21 | Simon; Morris | Daisy occluder and method for septal defect repair |
US5830221A (en) | 1996-09-20 | 1998-11-03 | United States Surgical Corporation | Coil fastener applier |
US6599316B2 (en) | 1996-11-04 | 2003-07-29 | Advanced Stent Technologies, Inc. | Extendible stent apparatus |
US5716397A (en) | 1996-12-06 | 1998-02-10 | Medtronic, Inc. | Annuloplasty device with removable stiffening element |
CA2272097C (en) | 1996-12-10 | 2007-02-20 | Purdue Research Foundation | Artificial vascular valves |
US6364901B1 (en) | 1996-12-20 | 2002-04-02 | Kanji Inoue | Appliance collapsible for insertion into a human organ and capable of resilient restoration |
US6352561B1 (en) | 1996-12-23 | 2002-03-05 | W. L. Gore & Associates | Implant deployment apparatus |
US6551350B1 (en) | 1996-12-23 | 2003-04-22 | Gore Enterprise Holdings, Inc. | Kink resistant bifurcated prosthesis |
US5935098A (en) | 1996-12-23 | 1999-08-10 | Conceptus, Inc. | Apparatus and method for accessing and manipulating the uterus |
EP0850607A1 (de) | 1996-12-31 | 1998-07-01 | Cordis Corporation | Klappenprothese zur Implantation in Körperkanälen |
US6183411B1 (en) | 1998-09-21 | 2001-02-06 | Myocor, Inc. | External stress reduction device and method |
US6406420B1 (en) | 1997-01-02 | 2002-06-18 | Myocor, Inc. | Methods and devices for improving cardiac function in hearts |
US6045497A (en) | 1997-01-02 | 2000-04-04 | Myocor, Inc. | Heart wall tension reduction apparatus and method |
US6050936A (en) | 1997-01-02 | 2000-04-18 | Myocor, Inc. | Heart wall tension reduction apparatus |
US5961440A (en) | 1997-01-02 | 1999-10-05 | Myocor, Inc. | Heart wall tension reduction apparatus and method |
US6074401A (en) | 1997-01-09 | 2000-06-13 | Coalescent Surgical, Inc. | Pinned retainer surgical fasteners, instruments and methods for minimally invasive vascular and endoscopic surgery |
US5961539A (en) | 1997-01-17 | 1999-10-05 | Segmed, Inc. | Method and apparatus for sizing, stabilizing and/or reducing the circumference of an anatomical structure |
DE69831935T2 (de) | 1997-01-24 | 2006-07-27 | Paragon Intellectual Properties, LLC, Charleston | Bistabiler federaufbau für ein stent |
US5702398A (en) | 1997-02-21 | 1997-12-30 | Tarabishy; Sam | Tension screw |
US5961549A (en) | 1997-04-03 | 1999-10-05 | Baxter International Inc. | Multi-leaflet bioprosthetic heart valve |
US5876373A (en) | 1997-04-04 | 1999-03-02 | Eclipse Surgical Technologies, Inc. | Steerable catheter |
AU2284497A (en) | 1997-04-11 | 1998-11-11 | Taccor, Inc. | Steerable catheter with rotatable tip electrode and method of use |
US5957949A (en) | 1997-05-01 | 1999-09-28 | World Medical Manufacturing Corp. | Percutaneous placement valve stent |
US6409755B1 (en) | 1997-05-29 | 2002-06-25 | Scimed Life Systems, Inc. | Balloon expandable stent with a self-expanding portion |
JP4162270B2 (ja) | 1997-06-27 | 2008-10-08 | ザ トラスティーズ オブ コロンビア ユニバーシティー イン ザ シティー オブ ニューヨーク | 循環弁修復のための装置 |
WO1999011201A2 (en) | 1997-09-04 | 1999-03-11 | Endocore, Inc. | Artificial chordae replacement |
FR2768324B1 (fr) | 1997-09-12 | 1999-12-10 | Jacques Seguin | Instrument chirurgical permettant, par voie percutanee, de fixer l'une a l'autre deux zones de tissu mou, normalement mutuellement distantes |
US5954766A (en) | 1997-09-16 | 1999-09-21 | Zadno-Azizi; Gholam-Reza | Body fluid flow control device |
US5984959A (en) | 1997-09-19 | 1999-11-16 | United States Surgical | Heart valve replacement tools and procedures |
US6206888B1 (en) | 1997-10-01 | 2001-03-27 | Scimed Life Systems, Inc. | Stent delivery system using shape memory retraction |
US5980565A (en) | 1997-10-20 | 1999-11-09 | Iowa-India Investments Company Limited | Sandwich stent |
US6120534A (en) | 1997-10-29 | 2000-09-19 | Ruiz; Carlos E. | Endoluminal prosthesis having adjustable constriction |
US6020646A (en) | 1997-12-05 | 2000-02-01 | The Charles Stark Draper Laboratory, Inc. | Intergrated circuit die assembly |
US6174332B1 (en) | 1997-12-05 | 2001-01-16 | St. Jude Medical, Inc. | Annuloplasty ring with cut zone |
US6332893B1 (en) | 1997-12-17 | 2001-12-25 | Myocor, Inc. | Valve to myocardium tension members device and method |
DE69841333D1 (de) | 1997-12-29 | 2010-01-07 | Cleveland Clinic Foundation | System zur minimalinvasiven einführung einer herzklappen- bioprothese |
US6530952B2 (en) | 1997-12-29 | 2003-03-11 | The Cleveland Clinic Foundation | Bioprosthetic cardiovascular valve system |
US6251092B1 (en) | 1997-12-30 | 2001-06-26 | Medtronic, Inc. | Deflectable guiding catheter |
EP1051128B1 (de) | 1998-01-30 | 2006-03-15 | St. Jude Medical ATG, Inc. | Medizinischer transplantatverbinder oder stopfen sowie verfahren zu ihrer herstellung |
US6533807B2 (en) | 1998-02-05 | 2003-03-18 | Medtronic, Inc. | Radially-expandable stent and delivery system |
US20020087048A1 (en) | 1998-02-24 | 2002-07-04 | Brock David L. | Flexible instrument |
FR2777446B1 (fr) | 1998-04-17 | 2000-12-01 | Perouse Implant Lab | Organe de liaison pour l'anastomose, dispositif de mise en place d'attaches et implant les comportant |
US6074418A (en) | 1998-04-20 | 2000-06-13 | St. Jude Medical, Inc. | Driver tool for heart valve prosthesis fasteners |
US6059827A (en) | 1998-05-04 | 2000-05-09 | Axya Medical, Inc. | Sutureless cardiac valve prosthesis, and devices and methods for implanting them |
US6143024A (en) | 1998-06-04 | 2000-11-07 | Sulzer Carbomedics Inc. | Annuloplasty ring having flexible anterior portion |
US6250308B1 (en) | 1998-06-16 | 2001-06-26 | Cardiac Concepts, Inc. | Mitral valve annuloplasty ring and method of implanting |
US6106550A (en) | 1998-07-10 | 2000-08-22 | Sulzer Carbomedics Inc. | Implantable attaching ring |
US6165183A (en) | 1998-07-15 | 2000-12-26 | St. Jude Medical, Inc. | Mitral and tricuspid valve repair |
US7569062B1 (en) | 1998-07-15 | 2009-08-04 | St. Jude Medical, Inc. | Mitral and tricuspid valve repair |
US6260552B1 (en) | 1998-07-29 | 2001-07-17 | Myocor, Inc. | Transventricular implant tools and devices |
US6264700B1 (en) | 1998-08-27 | 2001-07-24 | Endonetics, Inc. | Prosthetic gastroesophageal valve |
US6159240A (en) | 1998-08-31 | 2000-12-12 | Medtronic, Inc. | Rigid annuloplasty device that becomes compliant after implantation |
FR2783153B1 (fr) | 1998-09-14 | 2000-12-01 | Jerome Dargent | Dispositif de constriction gastrique |
US6334873B1 (en) | 1998-09-28 | 2002-01-01 | Autogenics | Heart valve having tissue retention with anchors and an outer sheath |
US6102945A (en) | 1998-10-16 | 2000-08-15 | Sulzer Carbomedics, Inc. | Separable annuloplasty ring |
US6113612A (en) | 1998-11-06 | 2000-09-05 | St. Jude Medical Cardiovascular Group, Inc. | Medical anastomosis apparatus |
US6152937A (en) | 1998-11-06 | 2000-11-28 | St. Jude Medical Cardiovascular Group, Inc. | Medical graft connector and methods of making and installing same |
US20040267349A1 (en) | 2003-06-27 | 2004-12-30 | Kobi Richter | Amorphous metal alloy medical devices |
US6254609B1 (en) | 1999-01-11 | 2001-07-03 | Scimed Life Systems, Inc. | Self-expanding stent delivery system with two sheaths |
US6558418B2 (en) | 1999-01-26 | 2003-05-06 | Edwards Lifesciences Corporation | Flexible heart valve |
US6736845B2 (en) | 1999-01-26 | 2004-05-18 | Edwards Lifesciences Corporation | Holder for flexible heart valve |
CA2358523C (en) | 1999-01-26 | 2009-08-18 | Edwards Lifesciences Corporation | Anatomical orifice sizers and methods of orifice sizing |
US6315784B1 (en) | 1999-02-03 | 2001-11-13 | Zarija Djurovic | Surgical suturing unit |
US6425916B1 (en) | 1999-02-10 | 2002-07-30 | Michi E. Garrison | Methods and devices for implanting cardiac valves |
AU3729400A (en) | 1999-03-09 | 2000-09-28 | St. Jude Medical Cardiovascular Group, Inc. | Medical grafting methods and apparatus |
DE19910233A1 (de) | 1999-03-09 | 2000-09-21 | Jostra Medizintechnik Ag | Anuloplastieprothese |
US6319281B1 (en) | 1999-03-22 | 2001-11-20 | Kumar R. Patel | Artificial venous valve and sizing catheter |
US8216256B2 (en) | 1999-04-09 | 2012-07-10 | Evalve, Inc. | Detachment mechanism for implantable fixation devices |
ATE492219T1 (de) | 1999-04-09 | 2011-01-15 | Evalve Inc | Vorrichtung zur herzklappenoperation |
US7604646B2 (en) | 1999-04-09 | 2009-10-20 | Evalve, Inc. | Locking mechanisms for fixation devices and methods of engaging tissue |
US10327743B2 (en) | 1999-04-09 | 2019-06-25 | Evalve, Inc. | Device and methods for endoscopic annuloplasty |
WO2006116558A2 (en) | 1999-04-09 | 2006-11-02 | Evalve, Inc. | Device and methods for endoscopic annuloplasty |
US6752813B2 (en) | 1999-04-09 | 2004-06-22 | Evalve, Inc. | Methods and devices for capturing and fixing leaflets in valve repair |
US7226467B2 (en) | 1999-04-09 | 2007-06-05 | Evalve, Inc. | Fixation device delivery catheter, systems and methods of use |
US7811296B2 (en) | 1999-04-09 | 2010-10-12 | Evalve, Inc. | Fixation devices for variation in engagement of tissue |
US20040044350A1 (en) | 1999-04-09 | 2004-03-04 | Evalve, Inc. | Steerable access sheath and methods of use |
US6183512B1 (en) | 1999-04-16 | 2001-02-06 | Edwards Lifesciences Corporation | Flexible annuloplasty system |
US6231602B1 (en) | 1999-04-16 | 2001-05-15 | Edwards Lifesciences Corporation | Aortic annuloplasty ring |
US20050222665A1 (en) | 1999-04-23 | 2005-10-06 | Ernest Aranyi | Endovascular fastener applicator |
US6764514B1 (en) | 1999-04-26 | 2004-07-20 | Sdgi Holdings, Inc. | Prosthetic apparatus and method |
US6674993B1 (en) | 1999-04-30 | 2004-01-06 | Microvision, Inc. | Method and system for identifying data locations associated with real world observations |
US6187040B1 (en) | 1999-05-03 | 2001-02-13 | John T. M. Wright | Mitral and tricuspid annuloplasty rings |
US6558396B1 (en) | 1999-05-06 | 2003-05-06 | Kanji Inoue | Apparatus for folding instrument and use of the same apparatus |
US6964686B2 (en) | 1999-05-17 | 2005-11-15 | Vanderbilt University | Intervertebral disc replacement prosthesis |
US6428550B1 (en) | 1999-05-18 | 2002-08-06 | Cardica, Inc. | Sutureless closure and deployment system for connecting blood vessels |
US6790229B1 (en) | 1999-05-25 | 2004-09-14 | Eric Berreklouw | Fixing device, in particular for fixing to vascular wall tissue |
US6287339B1 (en) | 1999-05-27 | 2001-09-11 | Sulzer Carbomedics Inc. | Sutureless heart valve prosthesis |
US7628803B2 (en) | 2001-02-05 | 2009-12-08 | Cook Incorporated | Implantable vascular device |
US6699256B1 (en) | 1999-06-04 | 2004-03-02 | St. Jude Medical Atg, Inc. | Medical grafting apparatus and methods |
US6602289B1 (en) | 1999-06-08 | 2003-08-05 | S&A Rings, Llc | Annuloplasty rings of particular use in surgery for the mitral valve |
US6626899B2 (en) | 1999-06-25 | 2003-09-30 | Nidus Medical, Llc | Apparatus and methods for treating tissue |
SE514718C2 (sv) | 1999-06-29 | 2001-04-09 | Jan Otto Solem | Anordning för behandling av bristande tillslutningsförmåga hos mitralisklaffapparaten |
US6997951B2 (en) | 1999-06-30 | 2006-02-14 | Edwards Lifesciences Ag | Method and device for treatment of mitral insufficiency |
US6312465B1 (en) | 1999-07-23 | 2001-11-06 | Sulzer Carbomedics Inc. | Heart valve prosthesis with a resiliently deformable retaining member |
US7462162B2 (en) | 2001-09-04 | 2008-12-09 | Broncus Technologies, Inc. | Antiproliferative devices for maintaining patency of surgically created channels in a body organ |
US6592609B1 (en) | 1999-08-09 | 2003-07-15 | Bonutti 2003 Trust-A | Method and apparatus for securing tissue |
US6231561B1 (en) | 1999-09-20 | 2001-05-15 | Appriva Medical, Inc. | Method and apparatus for closing a body lumen |
JP3553432B2 (ja) | 1999-09-24 | 2004-08-11 | 本田技研工業株式会社 | ライディングシミュレーション装置 |
US6533806B1 (en) | 1999-10-01 | 2003-03-18 | Scimed Life Systems, Inc. | Balloon yielded delivery system and endovascular graft design for easy deployment |
FR2799364B1 (fr) | 1999-10-12 | 2001-11-23 | Jacques Seguin | Dispositif d'annuloplastie utilisable par voie mini-invasive |
US6440164B1 (en) | 1999-10-21 | 2002-08-27 | Scimed Life Systems, Inc. | Implantable prosthetic valve |
US6626930B1 (en) | 1999-10-21 | 2003-09-30 | Edwards Lifesciences Corporation | Minimally invasive mitral valve repair method and apparatus |
US6626917B1 (en) | 1999-10-26 | 2003-09-30 | H. Randall Craig | Helical suture instrument |
AUPQ366099A0 (en) | 1999-10-26 | 1999-11-18 | Queensland University Of Technology | Ortho paedic screw |
US6689150B1 (en) | 1999-10-27 | 2004-02-10 | Atritech, Inc. | Filter apparatus for ostium of left atrial appendage |
US6926730B1 (en) | 2000-10-10 | 2005-08-09 | Medtronic, Inc. | Minimally invasive valve repair procedure and apparatus |
KR20010046894A (ko) | 1999-11-16 | 2001-06-15 | 오태준 | 전기면도기 |
US8579966B2 (en) | 1999-11-17 | 2013-11-12 | Medtronic Corevalve Llc | Prosthetic valve for transluminal delivery |
US8016877B2 (en) | 1999-11-17 | 2011-09-13 | Medtronic Corevalve Llc | Prosthetic valve for transluminal delivery |
US7018406B2 (en) | 1999-11-17 | 2006-03-28 | Corevalve Sa | Prosthetic valve for transluminal delivery |
US20070043435A1 (en) | 1999-11-17 | 2007-02-22 | Jacques Seguin | Non-cylindrical prosthetic valve system for transluminal delivery |
US6911032B2 (en) | 1999-11-18 | 2005-06-28 | Scimed Life Systems, Inc. | Apparatus and method for compressing body tissue |
US6458153B1 (en) | 1999-12-31 | 2002-10-01 | Abps Venture One, Ltd. | Endoluminal cardiac and venous valve prostheses and methods of manufacture and delivery thereof |
US6711444B2 (en) | 1999-11-22 | 2004-03-23 | Scimed Life Systems, Inc. | Methods of deploying helical diagnostic and therapeutic element supporting structures within the body |
US6602263B1 (en) | 1999-11-30 | 2003-08-05 | St. Jude Medical Atg, Inc. | Medical grafting methods and apparatus |
EP1108400A1 (de) | 1999-12-13 | 2001-06-20 | Biomedix S.A. | Abnehmbare Befestigungsvorrichtung für eine Prothese bestimmt für ein Körpergefäss |
US7169187B2 (en) | 1999-12-22 | 2007-01-30 | Ethicon, Inc. | Biodegradable stent |
US6494908B1 (en) | 1999-12-22 | 2002-12-17 | Ethicon, Inc. | Removable stent for body lumens |
US6942694B2 (en) | 2000-01-14 | 2005-09-13 | Viacor, Inc. | Tissue annuloplasty band and apparatus and method for fashioning, sizing and implanting the same |
NL1014095C2 (nl) | 2000-01-17 | 2001-07-18 | Cornelis Hendrikus Anna Witten | Implantaatklep voor implantatie in een bloedvat. |
US6769434B2 (en) | 2000-06-30 | 2004-08-03 | Viacor, Inc. | Method and apparatus for performing a procedure on a cardiac valve |
US7507252B2 (en) | 2000-01-31 | 2009-03-24 | Edwards Lifesciences Ag | Adjustable transluminal annuloplasty system |
US6989028B2 (en) | 2000-01-31 | 2006-01-24 | Edwards Lifesciences Ag | Medical system and method for remodeling an extravascular tissue structure |
DE60128069D1 (de) | 2000-01-31 | 2007-06-06 | Cook Biotech Inc | Stentventilklappen |
US6402781B1 (en) | 2000-01-31 | 2002-06-11 | Mitralife | Percutaneous mitral annuloplasty and cardiac reinforcement |
US6458076B1 (en) | 2000-02-01 | 2002-10-01 | 5 Star Medical | Multi-lumen medical device |
US6821297B2 (en) | 2000-02-02 | 2004-11-23 | Robert V. Snyders | Artificial heart valve, implantation instrument and method therefor |
US20050070999A1 (en) | 2000-02-02 | 2005-03-31 | Spence Paul A. | Heart valve repair apparatus and methods |
DE60111184T2 (de) | 2000-02-02 | 2005-10-27 | Robert V. Snyders | Künstiche herzklappe |
US6797002B2 (en) | 2000-02-02 | 2004-09-28 | Paul A. Spence | Heart valve repair apparatus and methods |
US6470892B1 (en) | 2000-02-10 | 2002-10-29 | Obtech Medical Ag | Mechanical heartburn and reflux treatment |
DE10010074B4 (de) | 2000-02-28 | 2005-04-14 | Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. | Vorrichtung zur Befestigung und Verankerung von Herzklappenprothesen |
US7993368B2 (en) | 2003-03-13 | 2011-08-09 | C.R. Bard, Inc. | Suture clips, delivery devices and methods |
US8474460B2 (en) | 2000-03-04 | 2013-07-02 | Pulmonx Corporation | Implanted bronchial isolation devices and methods |
WO2003028522A2 (en) | 2001-03-27 | 2003-04-10 | Neovasc Medical Ltd. | Flow reducing implant |
US6953476B1 (en) | 2000-03-27 | 2005-10-11 | Neovasc Medical Ltd. | Device and method for treating ischemic heart disease |
IL153753A0 (en) | 2002-12-30 | 2003-07-06 | Neovasc Medical Ltd | Varying-diameter vascular implant and balloon |
US6569198B1 (en) | 2000-03-31 | 2003-05-27 | Richard A. Wilson | Mitral or tricuspid valve annuloplasty prosthetic device |
US6689125B1 (en) | 2000-04-04 | 2004-02-10 | Spinalabs, Llc | Devices and methods for the treatment of spinal disorders |
US6454799B1 (en) | 2000-04-06 | 2002-09-24 | Edwards Lifesciences Corporation | Minimally-invasive heart valves and methods of use |
US6533772B1 (en) | 2000-04-07 | 2003-03-18 | Innex Corporation | Guide wire torque device |
US20020049490A1 (en) | 2000-04-11 | 2002-04-25 | Pollock David T. | Single-piece endoprosthesis with high expansion ratios |
US6497713B1 (en) | 2000-04-28 | 2002-12-24 | Autogenics | Rotary tissue cutting die |
US7083628B2 (en) | 2002-09-03 | 2006-08-01 | Edwards Lifesciences Corporation | Single catheter mitral valve repair device and method for use |
US6610088B1 (en) | 2000-05-03 | 2003-08-26 | Shlomo Gabbay | Biologically covered heart valve prosthesis |
WO2001087190A2 (en) | 2000-05-17 | 2001-11-22 | St. Jude Medical, Inc. | Two piece bioprosthetic heart valve |
US7220266B2 (en) | 2000-05-19 | 2007-05-22 | C. R. Bard, Inc. | Tissue capturing and suturing device and method |
WO2001089426A1 (fr) | 2000-05-25 | 2001-11-29 | Bioring S.A. | Dispositif pour retrecir et/ou renforcer les orifices valvulaires du coeur |
US8366769B2 (en) | 2000-06-01 | 2013-02-05 | Edwards Lifesciences Corporation | Low-profile, pivotable heart valve sewing ring |
US6805711B2 (en) | 2000-06-02 | 2004-10-19 | 3F Therapeutics, Inc. | Expandable medical implant and percutaneous delivery |
US6406493B1 (en) | 2000-06-02 | 2002-06-18 | Hosheng Tu | Expandable annuloplasty ring and methods of use |
US7632303B1 (en) | 2000-06-07 | 2009-12-15 | Advanced Cardiovascular Systems, Inc. | Variable stiffness medical devices |
SE522805C2 (sv) | 2000-06-22 | 2004-03-09 | Jan Otto Solem | Stentappliceringssystem |
ATE381291T1 (de) | 2000-06-23 | 2008-01-15 | Viacor Inc | Automatische ringförmige faltung zur mitralklappenreparatur |
US6676698B2 (en) | 2000-06-26 | 2004-01-13 | Rex Medicol, L.P. | Vascular device with valve for approximating vessel wall |
US7144414B2 (en) | 2000-06-27 | 2006-12-05 | Smith & Nephew, Inc. | Surgical procedures and instruments |
US7077861B2 (en) | 2000-07-06 | 2006-07-18 | Medtentia Ab | Annuloplasty instrument |
US6419696B1 (en) | 2000-07-06 | 2002-07-16 | Paul A. Spence | Annuloplasty devices and related heart valve repair methods |
US6613078B1 (en) | 2000-08-02 | 2003-09-02 | Hector Daniel Barone | Multi-component endoluminal graft assembly, use thereof and method of implanting |
SE0002878D0 (sv) | 2000-08-11 | 2000-08-11 | Kimblad Ola | Device and method for treatment of atrioventricular regurgitation |
US6524338B1 (en) | 2000-08-25 | 2003-02-25 | Steven R. Gundry | Method and apparatus for stapling an annuloplasty band in-situ |
AU2001287144A1 (en) | 2000-09-07 | 2002-03-22 | Viacor, Inc. | Fixation band for affixing a prosthetic heart valve to tissue |
US7510572B2 (en) | 2000-09-12 | 2009-03-31 | Shlomo Gabbay | Implantation system for delivery of a heart valve prosthesis |
US6554845B1 (en) | 2000-09-15 | 2003-04-29 | PARÉ Surgical, Inc. | Suturing apparatus and method |
US20060106278A1 (en) | 2004-05-14 | 2006-05-18 | Ample Medical, Inc. | Devices, systems, and methods for reshaping a heart valve annulus, including the use of an adjustable bridge implant system |
US8784482B2 (en) | 2000-09-20 | 2014-07-22 | Mvrx, Inc. | Method of reshaping a heart valve annulus using an intravascular device |
US6893459B1 (en) | 2000-09-20 | 2005-05-17 | Ample Medical, Inc. | Heart valve annulus device and method of using same |
US20080091264A1 (en) | 2002-11-26 | 2008-04-17 | Ample Medical, Inc. | Devices, systems, and methods for reshaping a heart valve annulus, including the use of magnetic tools |
US20090287179A1 (en) | 2003-10-01 | 2009-11-19 | Ample Medical, Inc. | Devices, systems, and methods for reshaping a heart valve annulus, including the use of magnetic tools |
US7381220B2 (en) | 2000-09-20 | 2008-06-03 | Ample Medical, Inc. | Devices, systems, and methods for supplementing, repairing, or replacing a native heart valve leaflet |
US6602288B1 (en) | 2000-10-05 | 2003-08-05 | Edwards Lifesciences Corporation | Minimally-invasive annuloplasty repair segment delivery template, system and method of use |
US6723038B1 (en) | 2000-10-06 | 2004-04-20 | Myocor, Inc. | Methods and devices for improving mitral valve function |
US6918917B1 (en) | 2000-10-10 | 2005-07-19 | Medtronic, Inc. | Minimally invasive annuloplasty procedure and apparatus |
US20020082525A1 (en) | 2000-10-18 | 2002-06-27 | Oslund John C. | Rapid exchange delivery catheter |
US6913608B2 (en) | 2000-10-23 | 2005-07-05 | Viacor, Inc. | Automated annular plication for mitral valve repair |
US6482228B1 (en) | 2000-11-14 | 2002-11-19 | Troy R. Norred | Percutaneous aortic valve replacement |
US6974476B2 (en) | 2003-05-05 | 2005-12-13 | Rex Medical, L.P. | Percutaneous aortic valve |
US6623510B2 (en) | 2000-12-07 | 2003-09-23 | Integrated Vascular Systems, Inc. | Closure device and methods for making and using them |
US6695867B2 (en) | 2002-02-21 | 2004-02-24 | Integrated Vascular Systems, Inc. | Plunger apparatus and methods for delivering a closure device |
US7211101B2 (en) | 2000-12-07 | 2007-05-01 | Abbott Vascular Devices | Methods for manufacturing a clip and clip |
US6716244B2 (en) | 2000-12-20 | 2004-04-06 | Carbomedics, Inc. | Sewing cuff assembly for heart valves |
US7591826B2 (en) | 2000-12-28 | 2009-09-22 | Cardiac Dimensions, Inc. | Device implantable in the coronary sinus to provide mitral valve therapy |
US7510576B2 (en) | 2001-01-30 | 2009-03-31 | Edwards Lifesciences Ag | Transluminal mitral annuloplasty |
US6810882B2 (en) | 2001-01-30 | 2004-11-02 | Ev3 Santa Rosa, Inc. | Transluminal mitral annuloplasty |
US20050182483A1 (en) | 2004-02-11 | 2005-08-18 | Cook Incorporated | Percutaneously placed prosthesis with thromboresistant valve portion |
US8038708B2 (en) | 2001-02-05 | 2011-10-18 | Cook Medical Technologies Llc | Implantable device with remodelable material and covering material |
JP4097924B2 (ja) | 2001-02-05 | 2008-06-11 | オリンパス株式会社 | 生体組織のクリップ装置 |
US6790231B2 (en) | 2001-02-05 | 2004-09-14 | Viacor, Inc. | Apparatus and method for reducing mitral regurgitation |
US6786924B2 (en) | 2001-03-15 | 2004-09-07 | Medtronic, Inc. | Annuloplasty band and method |
AUPR389201A0 (en) | 2001-03-23 | 2001-04-12 | Lane, Rodney James | Improvements in design of external vendus valve stents for the correction fo incompetent vendods valves |
US6733525B2 (en) | 2001-03-23 | 2004-05-11 | Edwards Lifesciences Corporation | Rolled minimally-invasive heart valves and methods of use |
US7556646B2 (en) | 2001-09-13 | 2009-07-07 | Edwards Lifesciences Corporation | Methods and apparatuses for deploying minimally-invasive heart valves |
US7374571B2 (en) | 2001-03-23 | 2008-05-20 | Edwards Lifesciences Corporation | Rolled minimally-invasive heart valves and methods of manufacture |
US7186264B2 (en) | 2001-03-29 | 2007-03-06 | Viacor, Inc. | Method and apparatus for improving mitral valve function |
DE60226719D1 (de) | 2001-04-02 | 2008-07-03 | Bladder Man Systems Llc | Anpassbarer ballonloser katheder |
US6958076B2 (en) | 2001-04-16 | 2005-10-25 | Biomedical Research Associates Inc. | Implantable venous valve |
DE10119096A1 (de) | 2001-04-19 | 2002-10-24 | Keramed Medizintechnik Gmbh | Biologisch funktionalisierte, metabolisch induktive Implantatoberflächen |
WO2005074367A2 (en) | 2004-02-03 | 2005-08-18 | Atria Medical Inc. | Device and method for controlling in-vivo pressure |
US20060069429A1 (en) | 2001-04-24 | 2006-03-30 | Spence Paul A | Tissue fastening systems and methods utilizing magnetic guidance |
WO2002085252A1 (en) | 2001-04-24 | 2002-10-31 | Dhc Systems, Inc. | Method and apparatus for catheter-based annuloplasty using local plications |
US8202315B2 (en) | 2001-04-24 | 2012-06-19 | Mitralign, Inc. | Catheter-based annuloplasty using ventricularly positioned catheter |
US20050125011A1 (en) | 2001-04-24 | 2005-06-09 | Spence Paul A. | Tissue fastening systems and methods utilizing magnetic guidance |
US6619291B2 (en) | 2001-04-24 | 2003-09-16 | Edwin J. Hlavka | Method and apparatus for catheter-based annuloplasty |
US7037334B1 (en) | 2001-04-24 | 2006-05-02 | Mitralign, Inc. | Method and apparatus for catheter-based annuloplasty using local plications |
GB0110551D0 (en) | 2001-04-30 | 2001-06-20 | Angiomed Ag | Self-expanding stent delivery service |
US6682558B2 (en) | 2001-05-10 | 2004-01-27 | 3F Therapeutics, Inc. | Delivery system for a stentless valve bioprosthesis |
ITMI20011012A1 (it) | 2001-05-17 | 2002-11-17 | Ottavio Alfieri | Protesi anulare per valvola mitrale |
FI114150B (fi) | 2001-05-17 | 2004-08-31 | Inion Ltd | Kirurgisten kiinnitysvälineiden kiinnitysvälinevarasto ja sovitelma kirurgisten kiinnnitysvälineiden kiinnitysvälinevarastolle |
US7935145B2 (en) | 2001-05-17 | 2011-05-03 | Edwards Lifesciences Corporation | Annuloplasty ring for ischemic mitral valve insuffuciency |
US6858039B2 (en) | 2002-07-08 | 2005-02-22 | Edwards Lifesciences Corporation | Mitral valve annuloplasty ring having a posterior bow |
US20030069635A1 (en) | 2001-05-29 | 2003-04-10 | Cartledge Richard G. | Prosthetic heart valve |
KR100393548B1 (ko) | 2001-06-05 | 2003-08-02 | 주식회사 엠아이텍 | 의료용 스텐트 |
EP1264532B1 (de) | 2001-06-06 | 2007-11-21 | Deere & Company | Rundballenpresse |
EP1266641B1 (de) | 2001-06-11 | 2004-10-06 | SORIN BIOMEDICA CARDIO S.p.A. | Annuloplastieprothese und Herstellungsverfahren dafür |
AU2002322255A1 (en) | 2001-06-15 | 2003-01-02 | The Cleveland Clinic Foundation | Tissue engineered mitral valve chrodae and methods of making and using same |
JP4159805B2 (ja) | 2001-06-15 | 2008-10-01 | ラディ・メディカル・システムズ・アクチェボラーグ | 閉鎖方法用の突き押し機構 |
US6958079B1 (en) | 2001-07-03 | 2005-10-25 | Reflux Corporation | Perorally insertable/removable anti-reflux valve |
FR2826863B1 (fr) | 2001-07-04 | 2003-09-26 | Jacques Seguin | Ensemble permettant la mise en place d'une valve prothetique dans un conduit corporel |
US7150737B2 (en) | 2001-07-13 | 2006-12-19 | Sci/Med Life Systems, Inc. | Methods and apparatuses for navigating the subarachnoid space |
US7377938B2 (en) | 2001-07-19 | 2008-05-27 | The Cleveland Clinic Foundation | Prosthetic cardiac value and method for making same |
FR2828263B1 (fr) | 2001-08-03 | 2007-05-11 | Philipp Bonhoeffer | Dispositif d'implantation d'un implant et procede d'implantation du dispositif |
US7179265B2 (en) | 2001-08-21 | 2007-02-20 | Microline Pentax, Inc. | Reduced diameter clip applying arrangement |
US6726716B2 (en) | 2001-08-24 | 2004-04-27 | Edwards Lifesciences Corporation | Self-molding annuloplasty ring |
US6908482B2 (en) | 2001-08-28 | 2005-06-21 | Edwards Lifesciences Corporation | Three-dimensional annuloplasty ring and template |
US6749630B2 (en) | 2001-08-28 | 2004-06-15 | Edwards Lifesciences Corporation | Tricuspid ring and template |
EP1432369B1 (de) | 2001-08-31 | 2008-02-27 | Mitral Interventions | Vorrichtung für eine herzklappenreperatur |
US7097659B2 (en) | 2001-09-07 | 2006-08-29 | Medtronic, Inc. | Fixation band for affixing a prosthetic heart valve to tissue |
US20030050693A1 (en) | 2001-09-10 | 2003-03-13 | Quijano Rodolfo C. | Minimally invasive delivery system for annuloplasty rings |
DE10148185B4 (de) | 2001-09-28 | 2005-08-11 | Alveolus, Inc. | Instrument zum Implantieren von Gefäßprothesen |
EP1434542A2 (de) | 2001-10-01 | 2004-07-07 | Ample Medical, Inc. | Verfahren und vorrichtungen für behandlungen von herzklappen |
US6893460B2 (en) | 2001-10-11 | 2005-05-17 | Percutaneous Valve Technologies Inc. | Implantable prosthetic valve |
US7144363B2 (en) | 2001-10-16 | 2006-12-05 | Extensia Medical, Inc. | Systems for heart treatment |
US20060020336A1 (en) | 2001-10-23 | 2006-01-26 | Liddicoat John R | Automated annular plication for mitral valve repair |
US7052487B2 (en) | 2001-10-26 | 2006-05-30 | Cohn William E | Method and apparatus for reducing mitral regurgitation |
GB0125925D0 (en) | 2001-10-29 | 2001-12-19 | Univ Glasgow | Mitral valve prosthesis |
US7311729B2 (en) | 2002-01-30 | 2007-12-25 | Cardiac Dimensions, Inc. | Device and method for modifying the shape of a body organ |
US6805710B2 (en) | 2001-11-13 | 2004-10-19 | Edwards Lifesciences Corporation | Mitral valve annuloplasty ring for molding left ventricle geometry |
US6575971B2 (en) | 2001-11-15 | 2003-06-10 | Quantum Cor, Inc. | Cardiac valve leaflet stapler device and methods thereof |
US20090099650A1 (en) | 2001-11-28 | 2009-04-16 | Lee Bolduc | Devices, systems, and methods for endovascular staple and/or prosthesis delivery and implantation |
US20050177180A1 (en) | 2001-11-28 | 2005-08-11 | Aptus Endosystems, Inc. | Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ |
CN100479786C (zh) | 2001-11-28 | 2009-04-22 | 阿普特斯内系统公司 | 血管内动脉瘤修复系统 |
US8231639B2 (en) | 2001-11-28 | 2012-07-31 | Aptus Endosystems, Inc. | Systems and methods for attaching a prosthesis within a body lumen or hollow organ |
US7137993B2 (en) | 2001-12-03 | 2006-11-21 | Xtent, Inc. | Apparatus and methods for delivery of multiple distributed stents |
US20030176914A1 (en) | 2003-01-21 | 2003-09-18 | Rabkin Dmitry J. | Multi-segment modular stent and methods for manufacturing stents |
AU2002228753A1 (en) | 2001-12-04 | 2003-06-17 | Edwards Lifesciences Corporation | Minimally-invasive annuloplasty repair segment delivery template system |
US6976995B2 (en) | 2002-01-30 | 2005-12-20 | Cardiac Dimensions, Inc. | Fixed length anchor and pull mitral valve device and method |
US7179282B2 (en) | 2001-12-05 | 2007-02-20 | Cardiac Dimensions, Inc. | Device and method for modifying the shape of a body organ |
US6908478B2 (en) | 2001-12-05 | 2005-06-21 | Cardiac Dimensions, Inc. | Anchor and pull mitral valve device and method |
US6978176B2 (en) | 2001-12-08 | 2005-12-20 | Lattouf Omar M | Treatment for patient with congestive heart failure |
DE10161543B4 (de) | 2001-12-11 | 2004-02-19 | REITAN, Öyvind | Implantat zur Behandlung einer Insuffizienz einer Herzklappe |
US6740107B2 (en) | 2001-12-19 | 2004-05-25 | Trimedyne, Inc. | Device for treatment of atrioventricular valve regurgitation |
EP1465555B1 (de) | 2001-12-21 | 2015-05-06 | QuickRing Medical Technologies Ltd. | Implantationssystem für anuloplastik-ringe |
US8123801B2 (en) | 2001-12-21 | 2012-02-28 | QuickRing Medical Technologies, Ltd. | Implantation system for annuloplasty rings |
US7201771B2 (en) | 2001-12-27 | 2007-04-10 | Arbor Surgical Technologies, Inc. | Bioprosthetic heart valve |
AU2002360066B2 (en) | 2001-12-28 | 2008-11-06 | Edwards Lifesciences Ag | Delayed memory device |
SE524709C2 (sv) | 2002-01-11 | 2004-09-21 | Edwards Lifesciences Ag | Anordning för fördröjd omformning av ett hjärtkärl och en hjärtklaff |
US7033390B2 (en) | 2002-01-02 | 2006-04-25 | Medtronic, Inc. | Prosthetic heart valve system |
US8308797B2 (en) | 2002-01-04 | 2012-11-13 | Colibri Heart Valve, LLC | Percutaneously implantable replacement heart valve device and method of making same |
US6764510B2 (en) | 2002-01-09 | 2004-07-20 | Myocor, Inc. | Devices and methods for heart valve treatment |
US20030139819A1 (en) | 2002-01-18 | 2003-07-24 | Beer Nicholas De | Method and apparatus for closing septal defects |
US7029482B1 (en) | 2002-01-22 | 2006-04-18 | Cardica, Inc. | Integrated anastomosis system |
US6989024B2 (en) | 2002-02-28 | 2006-01-24 | Counter Clockwise, Inc. | Guidewire loaded stent for delivery through a catheter |
US7048754B2 (en) | 2002-03-01 | 2006-05-23 | Evalve, Inc. | Suture fasteners and methods of use |
US8430934B2 (en) | 2002-03-01 | 2013-04-30 | Regents Of The University Of Minnesota | Vascular occlusion device |
US6797001B2 (en) | 2002-03-11 | 2004-09-28 | Cardiac Dimensions, Inc. | Device, assembly and method for mitral valve repair |
US6719786B2 (en) | 2002-03-18 | 2004-04-13 | Medtronic, Inc. | Flexible annuloplasty prosthesis and holder |
US7118595B2 (en) | 2002-03-18 | 2006-10-10 | Medtronic, Inc. | Flexible annuloplasty prosthesis and holder |
US7288111B1 (en) | 2002-03-26 | 2007-10-30 | Thoratec Corporation | Flexible stent and method of making the same |
US7094244B2 (en) | 2002-03-26 | 2006-08-22 | Edwards Lifesciences Corporation | Sequential heart valve leaflet repair device and method of use |
DE60234675D1 (de) | 2002-03-27 | 2010-01-21 | Sorin Biomedica Emodialisi S R | Anuloplastieprothese mit einem durchbohrten Bestandteil |
US20030199974A1 (en) | 2002-04-18 | 2003-10-23 | Coalescent Surgical, Inc. | Annuloplasty apparatus and methods |
WO2003088846A1 (en) | 2002-04-22 | 2003-10-30 | Tyco Healthcare Group, Lp | Tack and tack applier |
US7105016B2 (en) | 2002-04-23 | 2006-09-12 | Medtronic Vascular, Inc. | Integrated mechanical handle with quick slide mechanism |
US6951565B2 (en) | 2002-04-24 | 2005-10-04 | Linvatec Biomaterials Ltd. | Device for inserting surgical implants |
US7077850B2 (en) | 2002-05-01 | 2006-07-18 | Scimed Life Systems, Inc. | Tissue fastening devices and related insertion tools and methods |
EP1553892A1 (de) | 2002-05-09 | 2005-07-20 | Thomas D. Egan | Magenbypassprothese |
WO2003094795A1 (en) | 2002-05-10 | 2003-11-20 | Cordis Corporation | Method of making a medical device having a thin wall tubular membrane over a structural frame |
US7351256B2 (en) | 2002-05-10 | 2008-04-01 | Cordis Corporation | Frame based unidirectional flow prosthetic implant |
US6830638B2 (en) | 2002-05-24 | 2004-12-14 | Advanced Cardiovascular Systems, Inc. | Medical devices configured from deep drawn nickel-titanium alloys and nickel-titanium clad alloys and method of making the same |
ATE417549T1 (de) | 2002-06-04 | 2009-01-15 | Abbott Vascular Inc | Chirurgische klemme und anbringungsvorrichtung zur gefässwundverschliessung |
EP1521550A4 (de) | 2002-06-12 | 2011-02-23 | Mitral Interventions Inc | Verfahren und vorrichtung für eine gewebeverbindung |
US7588582B2 (en) | 2002-06-13 | 2009-09-15 | Guided Delivery Systems Inc. | Methods for remodeling cardiac tissue |
US7753924B2 (en) | 2003-09-04 | 2010-07-13 | Guided Delivery Systems, Inc. | Delivery devices and methods for heart valve repair |
US20060241656A1 (en) | 2002-06-13 | 2006-10-26 | Starksen Niel F | Delivery devices and methods for heart valve repair |
US6986775B2 (en) | 2002-06-13 | 2006-01-17 | Guided Delivery Systems, Inc. | Devices and methods for heart valve repair |
US7753922B2 (en) | 2003-09-04 | 2010-07-13 | Guided Delivery Systems, Inc. | Devices and methods for cardiac annulus stabilization and treatment |
US8641727B2 (en) | 2002-06-13 | 2014-02-04 | Guided Delivery Systems, Inc. | Devices and methods for heart valve repair |
US6679836B2 (en) | 2002-06-21 | 2004-01-20 | Scimed Life Systems, Inc. | Universal programmable guide catheter |
WO2004028399A2 (en) | 2002-06-28 | 2004-04-08 | Cook Incorporated | Thoracic deployment device |
US7608103B2 (en) | 2002-07-08 | 2009-10-27 | Edwards Lifesciences Corporation | Mitral valve annuloplasty ring having a posterior bow |
US7172625B2 (en) | 2002-07-16 | 2007-02-06 | Medtronic, Inc. | Suturing rings for implantable heart valve prostheses |
IL150855A (en) | 2002-07-22 | 2007-06-03 | Leonid Monassevitch | Intratubular anastomosis apparatus |
AU2003262683A1 (en) | 2002-08-13 | 2004-02-25 | The General Hospital Corporation | Cardiac devices and methods for percutaneous repair of atrioventricular valves |
US7041132B2 (en) | 2002-08-16 | 2006-05-09 | 3F Therapeutics, Inc, | Percutaneously delivered heart valve and delivery means thereof |
US7211114B2 (en) | 2002-08-26 | 2007-05-01 | The Trustees Of Columbia University In The City Of New York | Endoscopic gastric bypass |
EP1592367B1 (de) | 2002-08-28 | 2016-04-13 | HLT, Inc. | Verfahren und vorrichtung zur behandlung erkrankter klappen |
WO2007136783A2 (en) | 2002-08-29 | 2007-11-29 | Mitralsolutions, Inc. | Implantable devices for controlling the size and shape of an anatomical structure or lumen |
US8758372B2 (en) | 2002-08-29 | 2014-06-24 | St. Jude Medical, Cardiology Division, Inc. | Implantable devices for controlling the size and shape of an anatomical structure or lumen |
AU2003265852A1 (en) | 2002-08-29 | 2004-03-19 | Mitralsolutions, Inc. | Implantable devices for controlling the internal circumference of an anatomic orifice or lumen |
US20110009956A1 (en) | 2002-08-29 | 2011-01-13 | Cartledge Richard G | Magnetic docking system and method for the long term adjustment of an implantable device |
DE60221828T2 (de) | 2002-09-04 | 2008-05-08 | Endoart S.A. | Chirurgischer Ring mit Fernsteuerungseinrichtung für reversible Durchmesserveränderungen |
EP1572007B1 (de) | 2002-09-09 | 2011-12-28 | Brian Kelleher | Vorrichtung zur endoluminalen therapie |
US20040059413A1 (en) | 2002-09-20 | 2004-03-25 | Claudio Argento | Suture template for facilitating implantation of a prosthetic heart valve |
US7137184B2 (en) | 2002-09-20 | 2006-11-21 | Edwards Lifesciences Corporation | Continuous heart valve support frame and method of manufacture |
CO5500017A1 (es) | 2002-09-23 | 2005-03-31 | 3F Therapeutics Inc | Valvula mitral protesica |
US7149587B2 (en) | 2002-09-26 | 2006-12-12 | Pacesetter, Inc. | Cardiovascular anchoring device and method of deploying same |
AU2003277118A1 (en) | 2002-10-01 | 2004-04-23 | Ample Medical, Inc. | Devices for retaining native heart valve leaflet |
ATE418938T1 (de) | 2002-10-01 | 2009-01-15 | Ample Medical Inc | Vorrichtungen und systeme zur umformung eines herzklappen-annulus |
US7087064B1 (en) | 2002-10-15 | 2006-08-08 | Advanced Cardiovascular Systems, Inc. | Apparatuses and methods for heart valve repair |
US20050119735A1 (en) | 2002-10-21 | 2005-06-02 | Spence Paul A. | Tissue fastening systems and methods utilizing magnetic guidance |
JP2006503651A (ja) | 2002-10-21 | 2006-02-02 | ミトラリグン・インコーポレーテッド | ひだ形成を使用したカテーテルベースの環状形成手術を実行するための方法および装置 |
US6733536B1 (en) | 2002-10-22 | 2004-05-11 | Scimed Life Systems | Male urethral stent device |
AU2003274536A1 (en) | 2002-11-06 | 2004-06-07 | Koninklijke Philips Electronics N.V. | Method of adhesion measurement at the interface between layers |
US7247134B2 (en) | 2002-11-12 | 2007-07-24 | Myocor, Inc. | Devices and methods for heart valve treatment |
US7112219B2 (en) | 2002-11-12 | 2006-09-26 | Myocor, Inc. | Devices and methods for heart valve treatment |
US7335213B1 (en) | 2002-11-15 | 2008-02-26 | Abbott Cardiovascular Systems Inc. | Apparatus and methods for heart valve repair |
WO2004045378A2 (en) | 2002-11-15 | 2004-06-03 | The Government Of The United States Of America As Represented By The Secretary Of Health And Human Services | Method and device for catheter-based repair of cardiac valves |
US8187324B2 (en) | 2002-11-15 | 2012-05-29 | Advanced Cardiovascular Systems, Inc. | Telescoping apparatus for delivering and adjusting a medical device in a vessel |
US7485143B2 (en) | 2002-11-15 | 2009-02-03 | Abbott Cardiovascular Systems Inc. | Apparatuses and methods for heart valve repair |
US7404824B1 (en) | 2002-11-15 | 2008-07-29 | Advanced Cardiovascular Systems, Inc. | Valve aptation assist device |
US7608114B2 (en) | 2002-12-02 | 2009-10-27 | Gi Dynamics, Inc. | Bariatric sleeve |
US8551162B2 (en) | 2002-12-20 | 2013-10-08 | Medtronic, Inc. | Biologically implantable prosthesis |
US6984242B2 (en) | 2002-12-20 | 2006-01-10 | Gore Enterprise Holdings, Inc. | Implantable medical device assembly |
US7316710B1 (en) | 2002-12-30 | 2008-01-08 | Advanced Cardiovascular Systems, Inc. | Flexible stent |
US6849084B2 (en) | 2002-12-31 | 2005-02-01 | Intek Technology L.L.C. | Stent delivery system |
US6931338B2 (en) | 2003-01-07 | 2005-08-16 | Guide Technology, Inc. | System for providing a calibrated path for multi-signal cables in testing of integrated circuits |
US6830585B1 (en) | 2003-01-14 | 2004-12-14 | 3F Therapeutics, Inc. | Percutaneously deliverable heart valve and methods of implantation |
US7753945B2 (en) | 2003-01-17 | 2010-07-13 | Gore Enterprise Holdings, Inc. | Deployment system for an endoluminal device |
US7314485B2 (en) | 2003-02-03 | 2008-01-01 | Cardiac Dimensions, Inc. | Mitral valve device using conditioned shape memory alloy |
US20040176788A1 (en) | 2003-03-07 | 2004-09-09 | Nmt Medical, Inc. | Vacuum attachment system |
EP1608297A2 (de) | 2003-03-18 | 2005-12-28 | St. Jude Medical, Inc. | Gerät zur remodellierung von körpergewebe |
US20050107871A1 (en) | 2003-03-30 | 2005-05-19 | Fidel Realyvasquez | Apparatus and methods for valve repair |
CA2507649C (en) | 2003-04-02 | 2011-10-11 | Mehran Bashiri | Detachable and retrievable stent assembly |
US7159593B2 (en) | 2003-04-17 | 2007-01-09 | 3F Therapeutics, Inc. | Methods for reduction of pressure effects of cardiac tricuspid valve regurgitation |
US7530995B2 (en) | 2003-04-17 | 2009-05-12 | 3F Therapeutics, Inc. | Device for reduction of pressure effects of cardiac tricuspid valve regurgitation |
US7175656B2 (en) | 2003-04-18 | 2007-02-13 | Alexander Khairkhahan | Percutaneous transcatheter heart valve replacement |
ATE446061T1 (de) | 2003-04-24 | 2009-11-15 | Cook Inc | Künstliche klappe für blutgefäss mit verbessertem fliessverhalten |
US7717952B2 (en) | 2003-04-24 | 2010-05-18 | Cook Incorporated | Artificial prostheses with preferred geometries |
DE602004023350D1 (de) | 2003-04-30 | 2009-11-12 | Medtronic Vascular Inc | Perkutaneingesetzte provisorische Klappe |
US20040220593A1 (en) | 2003-05-01 | 2004-11-04 | Secant Medical, Llc | Restraining clip for mitral valve repair |
US20040230208A1 (en) | 2003-05-13 | 2004-11-18 | Vafa Shayani | Article for positioning mesh over tissue |
US10631871B2 (en) | 2003-05-19 | 2020-04-28 | Evalve, Inc. | Fixation devices, systems and methods for engaging tissue |
DE602004026858D1 (de) | 2003-05-20 | 2010-06-10 | Cleveland Clinic Foundation | Vorrichtung zur reparatur von herzklappen |
US7341584B1 (en) | 2003-05-30 | 2008-03-11 | Thomas David Starkey | Device and method to limit filling of the heart |
JP2007500583A (ja) | 2003-06-13 | 2007-01-18 | タイコ・ヘルスケア・グループ・リミテッド・パートナーシップ | 外科用器具のための複数部材相互接続および吸収性ねじファスナー |
US7967850B2 (en) | 2003-06-18 | 2011-06-28 | Jackson Roger P | Polyaxial bone anchor with helical capture connection, insert and dual locking assembly |
EP1648346A4 (de) | 2003-06-20 | 2006-10-18 | Medtronic Vascular Inc | Klappenöffnungsreduktionssystem |
US20040260394A1 (en) | 2003-06-20 | 2004-12-23 | Medtronic Vascular, Inc. | Cardiac valve annulus compressor system |
US7316706B2 (en) | 2003-06-20 | 2008-01-08 | Medtronic Vascular, Inc. | Tensioning device, system, and method for treating mitral valve regurgitation |
JP2007524460A (ja) | 2003-06-25 | 2007-08-30 | ジョージア テック リサーチ コーポレイション | 弁輪形成チェーン |
WO2005002424A2 (en) | 2003-07-02 | 2005-01-13 | Flexcor, Inc. | Annuloplasty rings and methods for repairing cardiac valves |
RU2006103367A (ru) | 2003-07-08 | 2006-06-27 | Вентор Текнолоджиз Лтд. (Il) | Имплантируемые протезные устройства, в частности, для трансартериальной доставки при лечении аортального стеноза и способы имплантации таких устройств |
US7201772B2 (en) | 2003-07-08 | 2007-04-10 | Ventor Technologies, Ltd. | Fluid flow prosthetic device |
NZ527025A (en) | 2003-07-16 | 2007-01-26 | David Peter Shaw | Prosthetic valves for medical application |
CA2533020A1 (en) | 2003-07-18 | 2005-03-03 | Ev3 Santa Rosa, Inc. | Remotely activated mitral annuloplasty system and methods |
US20050016560A1 (en) | 2003-07-21 | 2005-01-27 | Dee Voughlohn | Unique hair-styling system and method |
EP1653888B1 (de) | 2003-07-21 | 2009-09-09 | The Trustees of The University of Pennsylvania | Perkutane herzklappe |
DE10335648A1 (de) | 2003-07-30 | 2005-03-03 | Eberhard-Karls-Universität Tübingen | Verschlussstopfen für eine Öffnung in einer Wand eines Gefäßes oder Hohlorgans |
US7153324B2 (en) | 2003-07-31 | 2006-12-26 | Cook Incorporated | Prosthetic valve devices and methods of making such devices |
WO2005011535A2 (en) | 2003-07-31 | 2005-02-10 | Cook Incorporated | Prosthetic valve for implantation in a body vessel |
US8784472B2 (en) | 2003-08-15 | 2014-07-22 | Boston Scientific Scimed, Inc. | Clutch driven stent delivery system |
DE602004017750D1 (de) | 2003-08-19 | 2008-12-24 | Nmt Medical Inc | Expandierbarer Schleusenschlauch |
US8298280B2 (en) | 2003-08-21 | 2012-10-30 | Boston Scientific Scimed, Inc. | Stent with protruding branch portion for bifurcated vessels |
US8021421B2 (en) | 2003-08-22 | 2011-09-20 | Medtronic, Inc. | Prosthesis heart valve fixturing device |
US20050049692A1 (en) | 2003-09-02 | 2005-03-03 | Numamoto Michael J. | Medical device for reduction of pressure effects of cardiac tricuspid valve regurgitation |
US20070027549A1 (en) | 2003-09-02 | 2007-02-01 | Norman Godin | Gastrointestinal anti-reflux prosthesis apparatus and method |
US20050075725A1 (en) | 2003-10-02 | 2005-04-07 | Rowe Stanton J. | Implantable prosthetic valve with non-laminar flow |
US20050096738A1 (en) | 2003-10-06 | 2005-05-05 | Cali Douglas S. | Minimally invasive valve replacement system |
US20060259137A1 (en) | 2003-10-06 | 2006-11-16 | Jason Artof | Minimally invasive valve replacement system |
US10219899B2 (en) | 2004-04-23 | 2019-03-05 | Medtronic 3F Therapeutics, Inc. | Cardiac valve replacement systems |
US7553324B2 (en) | 2003-10-14 | 2009-06-30 | Xtent, Inc. | Fixed stent delivery devices and methods |
US7226647B2 (en) | 2003-10-16 | 2007-06-05 | Hewlett-Packard Development Company, L.P. | Permanent fixation of dyes to surface-modified inorganic particulate-coated media |
US7004176B2 (en) | 2003-10-17 | 2006-02-28 | Edwards Lifesciences Ag | Heart valve leaflet locator |
US20060184242A1 (en) | 2003-10-20 | 2006-08-17 | Samuel Lichtenstein | Method and apparatus for percutaneous reduction of anterior-posterior diameter of mitral valve |
ITBO20030631A1 (it) | 2003-10-23 | 2005-04-24 | Roberto Erminio Parravicini | Apparecchiatura protesica valvolare, in particolare per applicazioni cardiache. |
US20050090827A1 (en) | 2003-10-28 | 2005-04-28 | Tewodros Gedebou | Comprehensive tissue attachment system |
EP1680173B1 (de) | 2003-10-31 | 2011-01-12 | Trudell Medical International | System zur manipulierung eines katheters für die ablage einer substanz in einer körperhöhle |
US7473274B2 (en) | 2003-11-12 | 2009-01-06 | Medtronic Vascular, Inc. | Coronary sinus approach for repair of mitral valve regurgitation |
US7955384B2 (en) | 2003-11-12 | 2011-06-07 | Medtronic Vascular, Inc. | Coronary sinus approach for repair of mitral valve regurgitation |
US7655040B2 (en) | 2003-11-12 | 2010-02-02 | Medtronic Vascular, Inc. | Cardiac valve annulus reduction system |
IL158960A0 (en) | 2003-11-19 | 2004-05-12 | Neovasc Medical Ltd | Vascular implant |
WO2005055883A1 (en) | 2003-12-04 | 2005-06-23 | The Brigham And Women's Hospital, Inc. | Aortic valve annuloplasty rings |
US7186265B2 (en) | 2003-12-10 | 2007-03-06 | Medtronic, Inc. | Prosthetic cardiac valves and systems and methods for implanting thereof |
US20050177228A1 (en) | 2003-12-16 | 2005-08-11 | Solem Jan O. | Device for changing the shape of the mitral annulus |
US20050273138A1 (en) | 2003-12-19 | 2005-12-08 | Guided Delivery Systems, Inc. | Devices and methods for anchoring tissue |
US7887574B2 (en) | 2003-12-23 | 2011-02-15 | Scimed Life Systems, Inc. | Stent delivery catheter |
US7329279B2 (en) | 2003-12-23 | 2008-02-12 | Sadra Medical, Inc. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US8864822B2 (en) | 2003-12-23 | 2014-10-21 | Mitralign, Inc. | Devices and methods for introducing elements into tissue |
US9526609B2 (en) | 2003-12-23 | 2016-12-27 | Boston Scientific Scimed, Inc. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US8343213B2 (en) | 2003-12-23 | 2013-01-01 | Sadra Medical, Inc. | Leaflet engagement elements and methods for use thereof |
US7959666B2 (en) | 2003-12-23 | 2011-06-14 | Sadra Medical, Inc. | Methods and apparatus for endovascularly replacing a heart valve |
US7326236B2 (en) | 2003-12-23 | 2008-02-05 | Xtent, Inc. | Devices and methods for controlling and indicating the length of an interventional element |
US8182528B2 (en) | 2003-12-23 | 2012-05-22 | Sadra Medical, Inc. | Locking heart valve anchor |
US7824442B2 (en) | 2003-12-23 | 2010-11-02 | Sadra Medical, Inc. | Methods and apparatus for endovascularly replacing a heart valve |
US8287584B2 (en) | 2005-11-14 | 2012-10-16 | Sadra Medical, Inc. | Medical implant deployment tool |
US7748389B2 (en) | 2003-12-23 | 2010-07-06 | Sadra Medical, Inc. | Leaflet engagement elements and methods for use thereof |
US7445631B2 (en) | 2003-12-23 | 2008-11-04 | Sadra Medical, Inc. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US20050137686A1 (en) | 2003-12-23 | 2005-06-23 | Sadra Medical, A Delaware Corporation | Externally expandable heart valve anchor and method |
US7381219B2 (en) | 2003-12-23 | 2008-06-03 | Sadra Medical, Inc. | Low profile heart valve and delivery system |
US7780725B2 (en) | 2004-06-16 | 2010-08-24 | Sadra Medical, Inc. | Everting heart valve |
DE10394350B4 (de) | 2003-12-23 | 2018-05-17 | Cormove | In ein Lumen zu implantierender Teilesatz und Prothese denselben enthaltend |
CN101947146B (zh) | 2003-12-23 | 2014-08-06 | 萨德拉医学公司 | 可再定位的心脏瓣膜 |
US8052749B2 (en) | 2003-12-23 | 2011-11-08 | Sadra Medical, Inc. | Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements |
US20050137691A1 (en) | 2003-12-23 | 2005-06-23 | Sadra Medical | Two piece heart valve and anchor |
US7166127B2 (en) | 2003-12-23 | 2007-01-23 | Mitralign, Inc. | Tissue fastening systems and methods utilizing magnetic guidance |
US9005273B2 (en) | 2003-12-23 | 2015-04-14 | Sadra Medical, Inc. | Assessing the location and performance of replacement heart valves |
US8840663B2 (en) | 2003-12-23 | 2014-09-23 | Sadra Medical, Inc. | Repositionable heart valve method |
US8603160B2 (en) | 2003-12-23 | 2013-12-10 | Sadra Medical, Inc. | Method of using a retrievable heart valve anchor with a sheath |
US7288115B2 (en) | 2004-01-02 | 2007-10-30 | Zimmer Technology, Inc. | Multipart component for an orthopaedic implant |
US9254213B2 (en) | 2004-01-09 | 2016-02-09 | Rubicon Medical, Inc. | Stent delivery device |
US20050159728A1 (en) | 2004-01-15 | 2005-07-21 | Thomas Medical Products, Inc. | Steerable sheath |
US7871435B2 (en) | 2004-01-23 | 2011-01-18 | Edwards Lifesciences Corporation | Anatomically approximate prosthetic mitral heart valve |
US7597711B2 (en) | 2004-01-26 | 2009-10-06 | Arbor Surgical Technologies, Inc. | Heart valve assembly with slidable coupling connections |
US7311730B2 (en) | 2004-02-13 | 2007-12-25 | Shlomo Gabbay | Support apparatus and heart valve prosthesis for sutureless implantation |
US20050187568A1 (en) | 2004-02-20 | 2005-08-25 | Klenk Alan R. | Devices and methods for closing a patent foramen ovale with a coil-shaped closure device |
US7955375B2 (en) | 2004-02-20 | 2011-06-07 | Cook Medical Technologies Llc | Prosthetic valve with spacing member |
US8206439B2 (en) | 2004-02-23 | 2012-06-26 | International Heart Institute Of Montana Foundation | Internal prosthesis for reconstruction of cardiac geometry |
US8430925B2 (en) | 2004-02-27 | 2013-04-30 | Cardiacmd, Inc. | Prosthetic heart valves, scaffolding structures, and systems and methods for implantation of same |
ITTO20040135A1 (it) | 2004-03-03 | 2004-06-03 | Sorin Biomedica Cardio Spa | Protesi valvolare cardiaca |
US20050203606A1 (en) | 2004-03-09 | 2005-09-15 | Vancamp Daniel H. | Stent system for preventing restenosis |
US20050203549A1 (en) | 2004-03-09 | 2005-09-15 | Fidel Realyvasquez | Methods and apparatus for off pump aortic valve replacement with a valve prosthesis |
EP1734903B2 (de) | 2004-03-11 | 2022-01-19 | Percutaneous Cardiovascular Solutions Pty Limited | Perkutane herzklappenprothese |
US7942927B2 (en) | 2004-03-15 | 2011-05-17 | Baker Medical Research Institute | Treating valve failure |
NL1025830C2 (nl) | 2004-03-26 | 2005-02-22 | Eric Berreklouw | Samenstel omvattende een ring voor bevestiging in een door lichaamsweefsel omgeven doorgang alsmede een applicator voor het in de doorgang plaatsen van de ring. |
US8048140B2 (en) | 2004-03-31 | 2011-11-01 | Cook Medical Technologies Llc | Fenestrated intraluminal stent system |
US7993397B2 (en) | 2004-04-05 | 2011-08-09 | Edwards Lifesciences Ag | Remotely adjustable coronary sinus implant |
GB0407908D0 (en) | 2004-04-07 | 2004-05-12 | Univ York | Ionic liquids |
KR100819393B1 (ko) | 2004-04-08 | 2008-04-07 | 에이지에이 메디칼 코포레이션 | 플랜지가 형성된 폐색 장치 및 방법 |
US7294148B2 (en) | 2004-04-29 | 2007-11-13 | Edwards Lifesciences Corporation | Annuloplasty ring for mitral valve prolapse |
US7374573B2 (en) | 2004-05-03 | 2008-05-20 | Shlomo Gabbay | System and method for improving ventricular function |
US20050256566A1 (en) | 2004-05-03 | 2005-11-17 | Shlomo Gabbay | Apparatus and method for improving ventricular function |
JP5227588B2 (ja) | 2004-05-05 | 2013-07-03 | ダイレクト フロウ メディカル、 インク. | 現場形成支持構造を備えたステントレス心臓弁 |
US7390329B2 (en) | 2004-05-07 | 2008-06-24 | Usgi Medical, Inc. | Methods for grasping and cinching tissue anchors |
US20060122692A1 (en) | 2004-05-10 | 2006-06-08 | Ran Gilad | Stent valve and method of using same |
US20050256532A1 (en) | 2004-05-12 | 2005-11-17 | Asha Nayak | Cardiovascular defect patch device and method |
US7452376B2 (en) | 2004-05-14 | 2008-11-18 | St. Jude Medical, Inc. | Flexible, non-planar annuloplasty rings |
EP1768630B1 (de) | 2004-06-16 | 2015-01-07 | Machine Solutions, Inc. | Stent-Komprimiervorrichtung |
EP1765221A1 (de) | 2004-06-16 | 2007-03-28 | Cook Incorporated | Thorax-ablagevorrichtung und stent |
US8317859B2 (en) | 2004-06-28 | 2012-11-27 | J.W. Medical Systems Ltd. | Devices and methods for controlling expandable prostheses during deployment |
US20050288777A1 (en) | 2004-06-29 | 2005-12-29 | Rhee Richard S | Thermal conductor for adjustable cardiac valve implant |
US7276078B2 (en) | 2004-06-30 | 2007-10-02 | Edwards Lifesciences Pvt | Paravalvular leak detection, sealing, and prevention |
US7462191B2 (en) | 2004-06-30 | 2008-12-09 | Edwards Lifesciences Pvt, Inc. | Device and method for assisting in the implantation of a prosthetic valve |
US7556632B2 (en) | 2004-07-09 | 2009-07-07 | Reza Zadno | Device and method for repairing tissue |
US8308789B2 (en) | 2004-07-16 | 2012-11-13 | W. L. Gore & Associates, Inc. | Deployment system for intraluminal devices |
US8012202B2 (en) | 2004-07-27 | 2011-09-06 | Alameddine Abdallah K | Mitral valve ring for treatment of mitral valve regurgitation |
US20060041189A1 (en) | 2004-08-17 | 2006-02-23 | Vancaillie Thierry G | Grummet |
US7126289B2 (en) | 2004-08-20 | 2006-10-24 | O2 Micro Inc | Protection for external electrode fluorescent lamp system |
AU2005280145A1 (en) | 2004-08-27 | 2006-03-09 | Cook Incorporated | Placement of multiple intraluminal medical devices within a body vessel |
FR2874813B1 (fr) | 2004-09-07 | 2007-06-22 | Perouse Soc Par Actions Simpli | Prothese valvulaire |
US20060052867A1 (en) | 2004-09-07 | 2006-03-09 | Medtronic, Inc | Replacement prosthetic heart valve, system and method of implant |
WO2006032051A2 (en) | 2004-09-14 | 2006-03-23 | Edwards Lifesciences Ag | Device and method for treatment of heart valve regurgitation |
CA2581852C (en) | 2004-09-27 | 2012-11-13 | Evalve, Inc. | Methods and devices for tissue grasping and assessment |
US8052592B2 (en) | 2005-09-27 | 2011-11-08 | Evalve, Inc. | Methods and devices for tissue grasping and assessment |
US20060085012A1 (en) | 2004-09-28 | 2006-04-20 | Medtronic Vascular, Inc. | Torquing device delivered over a guidewire to rotate a medical fastener |
EP1799123B1 (de) | 2004-09-28 | 2015-05-06 | Surgical Solutions, LLC | Nahtanker |
US20070083168A1 (en) | 2004-09-30 | 2007-04-12 | Whiting James S | Transmembrane access systems and methods |
US6951571B1 (en) | 2004-09-30 | 2005-10-04 | Rohit Srivastava | Valve implanting device |
WO2006041877A2 (en) | 2004-10-05 | 2006-04-20 | Ample Medical, Inc. | Atrioventricular valve annulus repair systems and methods including retro-chordal anchors |
US7347868B2 (en) | 2004-10-26 | 2008-03-25 | Baronova, Inc. | Medical device delivery catheter |
WO2006050460A1 (en) | 2004-10-29 | 2006-05-11 | Cook Incorporated | Vascular valves having implanted and target configurations and methods of preparing the same |
US7470256B2 (en) | 2004-10-29 | 2008-12-30 | Merit Medical Systems, Inc., | Self-suturing anchor device for a catheter |
EP1807021B1 (de) | 2004-11-02 | 2011-05-04 | Machine Solutions, Inc. | Stentummantelungstechnologie |
US7455688B2 (en) | 2004-11-12 | 2008-11-25 | Con Interventional Systems, Inc. | Ostial stent |
US7744642B2 (en) | 2004-11-19 | 2010-06-29 | Biomedical Research Associates, Inc. | Prosthetic venous valves |
US8562672B2 (en) | 2004-11-19 | 2013-10-22 | Medtronic, Inc. | Apparatus for treatment of cardiac valves and method of its manufacture |
WO2006049629A1 (en) | 2004-11-24 | 2006-05-11 | Sunnyside Technologies Inc. | Devices and methods for beating heart cardiac surgeries |
JP4700608B2 (ja) | 2004-12-07 | 2011-06-15 | オリンパス株式会社 | 内視鏡用処置具システム、および、処置具が内包されたカートリッジ |
SE0403046D0 (sv) | 2004-12-15 | 2004-12-15 | Medtentia Ab | A device and method for improving the function of a heart valve |
IE20050841A1 (en) | 2004-12-15 | 2006-10-04 | Mednua Ltd | A medical device suitable for use in treatment of a valve |
US7355461B2 (en) | 2004-12-15 | 2008-04-08 | Asahi Kasei Microsystems Co., Ltd. | Waveform generating circuit and spread spectrum clock generator |
ATE435616T1 (de) | 2004-12-15 | 2009-07-15 | Cook Urological Inc | Röntgendichte manipulationsvorrichtungen |
US7758640B2 (en) | 2004-12-16 | 2010-07-20 | Valvexchange Inc. | Cardiovascular valve assembly |
US7578838B2 (en) | 2005-01-12 | 2009-08-25 | Cook Incorporated | Delivery system with helical shaft |
DE102005003632A1 (de) | 2005-01-20 | 2006-08-17 | Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. | Katheter für die transvaskuläre Implantation von Herzklappenprothesen |
WO2006086434A1 (en) | 2005-02-07 | 2006-08-17 | Evalve, Inc. | Methods, systems and devices for cardiac valve repair |
WO2011034628A1 (en) | 2005-02-07 | 2011-03-24 | Evalve, Inc. | Methods, systems and devices for cardiac valve repair |
CA2822801A1 (en) | 2005-02-07 | 2006-08-17 | Evalve, Inc. | Methods, systems and devices for cardiac valve repair |
US8220466B2 (en) | 2005-02-08 | 2012-07-17 | Koninklijke Philips Electronics N.V. | System and method for percutaneous palate remodeling |
ATE465673T1 (de) | 2005-02-08 | 2010-05-15 | Koninkl Philips Electronics Nv | System zur perkutanen glossoplastik |
ITTO20050074A1 (it) | 2005-02-10 | 2006-08-11 | Sorin Biomedica Cardio Srl | Protesi valvola cardiaca |
US20060195183A1 (en) | 2005-02-18 | 2006-08-31 | The Cleveland Clinic Foundation | Apparatus and methods for replacing a cardiac valve |
US8685086B2 (en) | 2006-02-18 | 2014-04-01 | The Cleveland Clinic Foundation | Apparatus and method for replacing a diseased cardiac valve |
US7717955B2 (en) | 2005-02-28 | 2010-05-18 | Medtronic, Inc. | Conformable prosthesis for implanting two-piece heart valves and methods for using them |
EP2649964B1 (de) | 2005-02-28 | 2019-07-24 | Medtentia International Ltd Oy | Vorrichtungen zur Verbesserung der Herzklappenfunktion |
US8083793B2 (en) | 2005-02-28 | 2011-12-27 | Medtronic, Inc. | Two piece heart valves including multiple lobe valves and methods for implanting them |
US7955385B2 (en) | 2005-02-28 | 2011-06-07 | Medtronic Vascular, Inc. | Device, system, and method for aiding valve annuloplasty |
US20070213810A1 (en) | 2005-03-14 | 2007-09-13 | Richard Newhauser | Segmented endoprosthesis |
US8608797B2 (en) | 2005-03-17 | 2013-12-17 | Valtech Cardio Ltd. | Mitral valve treatment techniques |
US8608726B2 (en) | 2005-03-24 | 2013-12-17 | The Cleveland Clinic Foundation | Vascular guidewire control apparatus |
US8864823B2 (en) | 2005-03-25 | 2014-10-21 | StJude Medical, Cardiology Division, Inc. | Methods and apparatus for controlling the internal circumference of an anatomic orifice or lumen |
US9492276B2 (en) | 2005-03-25 | 2016-11-15 | St. Jude Medical, Cardiology Division, Inc. | Methods and apparatus for controlling the internal circumference of an anatomic orifice or lumen |
US20060271171A1 (en) | 2005-04-01 | 2006-11-30 | Mcquinn Tim C | Artificial heart valve |
US8062359B2 (en) | 2005-04-06 | 2011-11-22 | Edwards Lifesciences Corporation | Highly flexible heart valve connecting band |
US7513909B2 (en) | 2005-04-08 | 2009-04-07 | Arbor Surgical Technologies, Inc. | Two-piece prosthetic valves with snap-in connection and methods for use |
US7722666B2 (en) | 2005-04-15 | 2010-05-25 | Boston Scientific Scimed, Inc. | Valve apparatus, system and method |
WO2006113906A1 (en) | 2005-04-20 | 2006-10-26 | The Cleveland Clinic Foundation | Apparatus and method for replacing a cardiac valve |
SE531468C2 (sv) | 2005-04-21 | 2009-04-14 | Edwards Lifesciences Ag | En anordning för styrning av blodflöde |
US8333777B2 (en) | 2005-04-22 | 2012-12-18 | Benvenue Medical, Inc. | Catheter-based tissue remodeling devices and methods |
US7914569B2 (en) | 2005-05-13 | 2011-03-29 | Medtronics Corevalve Llc | Heart valve prosthesis and methods of manufacture and use |
FR2885794B1 (fr) | 2005-05-19 | 2007-08-17 | Perouse Soc Par Actions Simpli | Necessaire de largage d'un organe de traitement d'une cavite et procede de preparation d'un organe de traitement associe |
WO2006127756A2 (en) | 2005-05-24 | 2006-11-30 | Edwards Lifesciences Corporation | Rapid deployment prosthetic heart valve |
US8317855B2 (en) | 2005-05-26 | 2012-11-27 | Boston Scientific Scimed, Inc. | Crimpable and expandable side branch cell |
WO2006130505A2 (en) | 2005-05-27 | 2006-12-07 | Arbor Surgical Technologies, Inc. | Gasket with collar for prosthetic heart valves and methods for using them |
EP3482717B1 (de) | 2005-05-27 | 2023-09-06 | Edwards Lifesciences Corporation | Stentlose trägerstruktur |
US7500989B2 (en) | 2005-06-03 | 2009-03-10 | Edwards Lifesciences Corp. | Devices and methods for percutaneous repair of the mitral valve via the coronary sinus |
US7938851B2 (en) | 2005-06-08 | 2011-05-10 | Xtent, Inc. | Devices and methods for operating and controlling interventional apparatus |
US20060287716A1 (en) | 2005-06-08 | 2006-12-21 | The Cleveland Clinic Foundation | Artificial chordae |
US7780723B2 (en) | 2005-06-13 | 2010-08-24 | Edwards Lifesciences Corporation | Heart valve delivery system |
US8951285B2 (en) | 2005-07-05 | 2015-02-10 | Mitralign, Inc. | Tissue anchor, anchoring system and methods of using the same |
US20070162111A1 (en) | 2005-07-06 | 2007-07-12 | The Cleveland Clinic Foundation | Apparatus and method for replacing a cardiac valve |
US20070016288A1 (en) | 2005-07-13 | 2007-01-18 | Gurskis Donnell W | Two-piece percutaneous prosthetic heart valves and methods for making and using them |
US7682391B2 (en) | 2005-07-13 | 2010-03-23 | Edwards Lifesciences Corporation | Methods of implanting a prosthetic mitral heart valve having a contoured sewing ring |
DE102006017873A1 (de) | 2005-07-14 | 2007-01-25 | Qualimed Innovative Medizinprodukte Gmbh | Temporärer Stent |
US7927371B2 (en) | 2005-07-15 | 2011-04-19 | The Cleveland Clinic Foundation | Apparatus and method for reducing cardiac valve regurgitation |
WO2007011799A1 (en) | 2005-07-15 | 2007-01-25 | The Cleveland Clinic Foundation | Apparatus and method for remodeling a cardiac valve annulus |
US7875056B2 (en) | 2005-07-22 | 2011-01-25 | Anpa Medical, Inc. | Wedge operated retainer device and methods |
WO2007016097A2 (en) | 2005-07-27 | 2007-02-08 | Georgia Tech Research Corporation | Implantable prosthetic vascular valve |
US20070027533A1 (en) | 2005-07-28 | 2007-02-01 | Medtronic Vascular, Inc. | Cardiac valve annulus restraining device |
EP1919398B1 (de) | 2005-07-29 | 2014-03-05 | Cook Medical Technologies LLC | Elliptische implantierbare vorrichtung |
US20070055206A1 (en) | 2005-08-10 | 2007-03-08 | Guided Delivery Systems, Inc. | Methods and devices for deployment of tissue anchors |
US20070038295A1 (en) | 2005-08-12 | 2007-02-15 | Cook Incorporated | Artificial valve prosthesis having a ring frame |
US20070055358A1 (en) | 2005-08-22 | 2007-03-08 | Krolik Jeffrey A | Axially compressible flared stents and apparatus and methods for delivering them |
US7611534B2 (en) | 2005-08-25 | 2009-11-03 | The Cleveland Clinic Foundation | Percutaneous atrioventricular valve and method of use |
US9492277B2 (en) | 2005-08-30 | 2016-11-15 | Mayo Foundation For Medical Education And Research | Soft body tissue remodeling methods and apparatus |
US20070078297A1 (en) | 2005-08-31 | 2007-04-05 | Medtronic Vascular, Inc. | Device for Treating Mitral Valve Regurgitation |
US7846179B2 (en) | 2005-09-01 | 2010-12-07 | Ovalis, Inc. | Suture-based systems and methods for treating septal defects |
AU2006287211B2 (en) | 2005-09-01 | 2012-09-27 | Cardinal Health 529, Llc | Patent foramen ovale closure method |
US8968379B2 (en) | 2005-09-02 | 2015-03-03 | Medtronic Vascular, Inc. | Stent delivery system with multiple evenly spaced pullwires |
CA2872116C (en) | 2005-09-07 | 2017-02-28 | Medtentia International Ltd Oy | A device for improving the function of a heart valve |
US7731741B2 (en) | 2005-09-08 | 2010-06-08 | Boston Scientific Scimed, Inc. | Inflatable bifurcation stent |
US20070061010A1 (en) | 2005-09-09 | 2007-03-15 | Hauser David L | Device and method for reshaping mitral valve annulus |
US7530253B2 (en) | 2005-09-09 | 2009-05-12 | Edwards Lifesciences Corporation | Prosthetic valve crimping device |
US7569071B2 (en) | 2005-09-21 | 2009-08-04 | Boston Scientific Scimed, Inc. | Venous valve, system, and method with sinus pocket |
WO2007038540A1 (en) | 2005-09-26 | 2007-04-05 | Medtronic, Inc. | Prosthetic cardiac and venous valves |
CA2561034C (en) | 2005-09-30 | 2014-12-09 | Sherwood Services Ag | Flexible endoscopic catheter with an end effector for coagulating and transfecting tissue |
US7695510B2 (en) | 2005-10-11 | 2010-04-13 | Medtronic Vascular, Inc. | Annuloplasty device having shape-adjusting tension filaments |
US8167932B2 (en) | 2005-10-18 | 2012-05-01 | Edwards Lifesciences Corporation | Heart valve delivery system with valve catheter |
US8038720B2 (en) | 2005-10-18 | 2011-10-18 | Wallace Jeffrey M | Methods and devices for intragastrointestinal prostheses |
CN101466316B (zh) | 2005-10-20 | 2012-06-27 | 阿普特斯内系统公司 | 包括使用固定件工具的用于修复物递送和植入的装置、系统和方法 |
DE102005051849B4 (de) | 2005-10-28 | 2010-01-21 | JenaValve Technology Inc., Wilmington | Vorrichtung zur Implantation und Befestigung von Herzklappenprothesen |
US8343204B2 (en) | 2005-10-31 | 2013-01-01 | Cook Medical Technologies Llc | Composite stent graft |
DE102005052628B4 (de) | 2005-11-04 | 2014-06-05 | Jenavalve Technology Inc. | Selbstexpandierendes, flexibles Drahtgeflecht mit integrierter Klappenprothese für den transvaskulären Herzklappenersatz und ein System mit einer solchen Vorrichtung und einem Einführkatheter |
EP1951352B1 (de) | 2005-11-10 | 2017-01-11 | Edwards Lifesciences CardiAQ LLC | Ballon-expandierbarer, selbst-expandierbarer gefässprothesen-verbindungsstent |
WO2007059483A2 (en) | 2005-11-14 | 2007-05-24 | Ev3, Inc. | Stent and stent delivery system for ostial locations in a conduit |
US20070112418A1 (en) | 2005-11-14 | 2007-05-17 | Boston Scientific Scimed, Inc. | Stent with spiral side-branch support designs |
EP1790318B1 (de) | 2005-11-16 | 2009-04-22 | Micardia Corporation | Magnetische Befestigung eines Katheters an ein Implantat |
US8764820B2 (en) | 2005-11-16 | 2014-07-01 | Edwards Lifesciences Corporation | Transapical heart valve delivery system and method |
WO2007062054A2 (en) | 2005-11-21 | 2007-05-31 | The Brigham And Women's Hospital, Inc. | Percutaneous cardiac valve repair with adjustable artificial chordae |
US7632308B2 (en) | 2005-11-23 | 2009-12-15 | Didier Loulmet | Methods, devices, and kits for treating mitral valve prolapse |
US8043368B2 (en) | 2005-11-23 | 2011-10-25 | Traves Dean Crabtree | Methods and apparatus for atrioventricular valve repair |
CA2669188C (en) | 2005-12-15 | 2014-08-05 | Georgia Tech Research Corporation | Papillary muscle position control devices, systems, & methods |
EP1959865B1 (de) | 2005-12-15 | 2014-12-10 | The Cleveland Clinic Foundation | Gerät zur behandlung von klappen-regurgitation |
US20070142907A1 (en) | 2005-12-16 | 2007-06-21 | Micardia Corporation | Adjustable prosthetic valve implant |
US20070213813A1 (en) | 2005-12-22 | 2007-09-13 | Symetis Sa | Stent-valves for valve replacement and associated methods and systems for surgery |
EP1803420B1 (de) | 2005-12-28 | 2009-07-01 | Sorin Biomedica Cardio S.R.L. | Prothese für Annuloplastie mit auxetischer Struktur |
US9375215B2 (en) | 2006-01-20 | 2016-06-28 | W. L. Gore & Associates, Inc. | Device for rapid repair of body conduits |
US7967857B2 (en) | 2006-01-27 | 2011-06-28 | Medtronic, Inc. | Gasket with spring collar for prosthetic heart valves and methods for making and using them |
WO2008029296A2 (en) | 2006-02-16 | 2008-03-13 | Endocor Pte Ltd. | Minimally invasive heart valve replacement |
US8403981B2 (en) | 2006-02-27 | 2013-03-26 | CardiacMC, Inc. | Methods and devices for delivery of prosthetic heart valves and other prosthetics |
US7635386B1 (en) | 2006-03-07 | 2009-12-22 | University Of Maryland, Baltimore | Methods and devices for performing cardiac valve repair |
US7431692B2 (en) | 2006-03-09 | 2008-10-07 | Edwards Lifesciences Corporation | Apparatus, system, and method for applying and adjusting a tensioning element to a hollow body organ |
EP1998719A1 (de) | 2006-03-10 | 2008-12-10 | Arbor Surgical Technologies, Inc. | Ventileinführungsvorrichtungen sowie verfahren zu ihrer herstellung und verwendung |
US20070219558A1 (en) | 2006-03-15 | 2007-09-20 | Allen Deutsch | Method and apparatus for arthroscopic surgery using suture anchors |
US20070225759A1 (en) | 2006-03-22 | 2007-09-27 | Daniel Thommen | Method for delivering a medical device to the heart of a patient |
DE102006013770A1 (de) | 2006-03-24 | 2007-09-27 | Occlutech Gmbh | Occlusionsinstrument und Verfahren zu dessen Herstellung |
WO2007123658A1 (en) | 2006-03-28 | 2007-11-01 | Medtronic, Inc. | Prosthetic cardiac valve formed from pericardium material and methods of making same |
WO2007115110A2 (en) | 2006-03-29 | 2007-10-11 | The Catheter Exchange, Inc. | Method and device for cavity obliteration |
CN101049269B (zh) | 2006-04-03 | 2010-12-29 | 孟坚 | 医疗用闭塞器械 |
US7625403B2 (en) | 2006-04-04 | 2009-12-01 | Medtronic Vascular, Inc. | Valved conduit designed for subsequent catheter delivered valve therapy |
US20070239208A1 (en) | 2006-04-05 | 2007-10-11 | Crawford Bruce S | Surgical implantation device and method |
US7524331B2 (en) | 2006-04-06 | 2009-04-28 | Medtronic Vascular, Inc. | Catheter delivered valve having a barrier to provide an enhanced seal |
US7591848B2 (en) | 2006-04-06 | 2009-09-22 | Medtronic Vascular, Inc. | Riveted stent valve for percutaneous use |
US7699892B2 (en) | 2006-04-12 | 2010-04-20 | Medtronic Vascular, Inc. | Minimally invasive procedure for implanting an annuloplasty device |
US20070244555A1 (en) | 2006-04-12 | 2007-10-18 | Medtronic Vascular, Inc. | Annuloplasty Device Having a Helical Anchor and Methods for its Use |
WO2007121314A2 (en) | 2006-04-12 | 2007-10-25 | Medtronic Vascular, Inc. | Annuloplasty device having a helical anchor and methods for its use |
US20070244546A1 (en) | 2006-04-18 | 2007-10-18 | Medtronic Vascular, Inc. | Stent Foundation for Placement of a Stented Valve |
WO2007124076A1 (en) | 2006-04-21 | 2007-11-01 | Abbott Laboratories | Guidewire handling device |
US7442207B2 (en) | 2006-04-21 | 2008-10-28 | Medtronic Vascular, Inc. | Device, system, and method for treating cardiac valve regurgitation |
US8551161B2 (en) | 2006-04-25 | 2013-10-08 | Medtronic Vascular, Inc. | Cardiac valve annulus restraining device |
WO2007136532A2 (en) | 2006-05-03 | 2007-11-29 | St. Jude Medical, Inc. | Soft body tissue remodeling methods and apparatus |
JP2009536074A (ja) | 2006-05-05 | 2009-10-08 | チルドレンズ・メディカル・センター・コーポレイション | 経カテーテル人工心臓弁 |
ATE499074T1 (de) | 2006-05-15 | 2011-03-15 | Edwards Lifesciences Ag | System zur veränderung der geometrie des herzens |
US20080234660A2 (en) | 2006-05-16 | 2008-09-25 | Sarah Cumming | Steerable Catheter Using Flat Pull Wires and Method of Making Same |
US8932348B2 (en) | 2006-05-18 | 2015-01-13 | Edwards Lifesciences Corporation | Device and method for improving heart valve function |
US20070276437A1 (en) | 2006-05-25 | 2007-11-29 | Mitralign, Inc. | Lockers for surgical tensioning members and methods of using the same to secure surgical tensioning members |
US7811316B2 (en) | 2006-05-25 | 2010-10-12 | Deep Vein Medical, Inc. | Device for regulating blood flow |
CA2652471C (en) | 2006-06-01 | 2014-09-09 | Edwards Lifesciences Corporation | Prosthetic insert for improving heart valve function |
ITTO20060413A1 (it) | 2006-06-07 | 2007-12-08 | Arrigo Lessana | Dispositivo sostitutivo delle corde tendinee di una valvola atrioventricolare |
BRPI0713403A2 (pt) | 2006-06-14 | 2012-03-13 | Optivia Medical Llc | Sistemas e métodos de introdução de dispositivo médico |
CA2657433A1 (en) | 2006-06-20 | 2007-12-27 | Aortx, Inc. | Torque shaft and torque drive |
EP2034929A4 (de) | 2006-06-20 | 2010-04-07 | Aortx Inc | Herzklappenprothese, trägerstrukturen sowie systeme und verfahren zur prothesenimplantierung |
US8142492B2 (en) | 2006-06-21 | 2012-03-27 | Aortx, Inc. | Prosthetic valve implantation systems |
US7934506B2 (en) | 2006-06-21 | 2011-05-03 | Koninklijke Philips Electronics N.V. | System and method for temporary tongue suspension |
US20070295172A1 (en) | 2006-06-23 | 2007-12-27 | Darian Swartz | Fastener Holding Device |
US8449605B2 (en) | 2006-06-28 | 2013-05-28 | Kardium Inc. | Method for anchoring a mitral valve |
US7955315B2 (en) | 2006-07-24 | 2011-06-07 | Ethicon, Inc. | Articulating laparoscopic device and method for delivery of medical fluid |
WO2008013915A2 (en) | 2006-07-28 | 2008-01-31 | Arshad Quadri | Percutaneous valve prosthesis and system and method for implanting same |
US7871432B2 (en) | 2006-08-02 | 2011-01-18 | Medtronic, Inc. | Heart valve holder for use in valve implantation procedures |
US8840655B2 (en) | 2006-08-09 | 2014-09-23 | Coherex Medical, Inc. | Systems and devices for reducing the size of an internal tissue opening |
US8529597B2 (en) | 2006-08-09 | 2013-09-10 | Coherex Medical, Inc. | Devices for reducing the size of an internal tissue opening |
US8430926B2 (en) | 2006-08-11 | 2013-04-30 | Japd Consulting Inc. | Annuloplasty with enhanced anchoring to the annulus based on tissue healing |
US20080039935A1 (en) | 2006-08-14 | 2008-02-14 | Wally Buch | Methods and apparatus for mitral valve repair |
US20080097595A1 (en) | 2006-08-22 | 2008-04-24 | Shlomo Gabbay | Intraventricular cardiac prosthesis |
WO2008031103A2 (en) | 2006-09-08 | 2008-03-13 | Edwards Lifesciences Corporation | Integrated heart valve delivery system |
US8876895B2 (en) | 2006-09-19 | 2014-11-04 | Medtronic Ventor Technologies Ltd. | Valve fixation member having engagement arms |
US20080082083A1 (en) | 2006-09-28 | 2008-04-03 | Forde Sean T | Perforated expandable implant recovery sheath |
FR2906454B1 (fr) | 2006-09-28 | 2009-04-10 | Perouse Soc Par Actions Simpli | Implant destine a etre place dans un conduit de circulation du sang. |
ATE544428T1 (de) | 2006-09-28 | 2012-02-15 | Cook Medical Technologies Llc | Vorrichtung zur reparatur von aortenaneurysmen im brustkorb |
US7534261B2 (en) | 2006-10-02 | 2009-05-19 | Edwards Lifesciences Corporation | Sutureless heart valve attachment |
US8029556B2 (en) | 2006-10-04 | 2011-10-04 | Edwards Lifesciences Corporation | Method and apparatus for reshaping a ventricle |
US8163011B2 (en) | 2006-10-06 | 2012-04-24 | BioStable Science & Engineering, Inc. | Intra-annular mounting frame for aortic valve repair |
US7674276B2 (en) | 2006-10-06 | 2010-03-09 | Biomet Sports Medicine, Llc | Rotational securing of a suture |
US7879087B2 (en) | 2006-10-06 | 2011-02-01 | Edwards Lifesciences Corporation | Mitral and tricuspid annuloplasty rings |
WO2008046092A2 (en) | 2006-10-13 | 2008-04-17 | Creighton University | Implantable valve prosthesis |
US8388680B2 (en) | 2006-10-18 | 2013-03-05 | Guided Delivery Systems, Inc. | Methods and devices for catheter advancement and delivery of substances therethrough |
US7935144B2 (en) | 2006-10-19 | 2011-05-03 | Direct Flow Medical, Inc. | Profile reduction of valve implant |
US20090248143A1 (en) | 2006-10-24 | 2009-10-01 | Beth Israel Deaconess Medical Center | Percutaneous aortic valve assembly |
US7771467B2 (en) | 2006-11-03 | 2010-08-10 | The Cleveland Clinic Foundation | Apparatus for repairing the function of a native aortic valve |
EP3329860A1 (de) | 2006-11-07 | 2018-06-06 | David Stephen Celermajer | Vorrichtungen zur behandlung von herzversagen |
SE530568C2 (sv) | 2006-11-13 | 2008-07-08 | Medtentia Ab | Anordning och metod för förbättring av funktionen hos en hjärtklaff |
CA2671966A1 (en) | 2006-12-05 | 2008-06-12 | Valtech Cardio, Ltd. | Segmented ring placement |
JP5593545B2 (ja) | 2006-12-06 | 2014-09-24 | メドトロニック シーブイ ルクセンブルク エス.アー.エール.エル. | 弁輪に固定された自己拡張型弁の経心尖的送達のためのシステムおよび方法 |
US20080140003A1 (en) | 2006-12-06 | 2008-06-12 | Advanced Cardiovascular Systems, Inc. | Balloon catheter having a regrooming sheath and method for collapsing an expanded medical device |
US8070799B2 (en) | 2006-12-19 | 2011-12-06 | Sorin Biomedica Cardio S.R.L. | Instrument and method for in situ deployment of cardiac valve prostheses |
US8236045B2 (en) | 2006-12-22 | 2012-08-07 | Edwards Lifesciences Corporation | Implantable prosthetic valve assembly and method of making the same |
MX2009007289A (es) | 2007-01-03 | 2009-09-09 | Mitralsolutions Inc | Dispositivos implantables para controlar el tamaño y la forma de una estructura o lumen anatomico. |
US8133270B2 (en) | 2007-01-08 | 2012-03-13 | California Institute Of Technology | In-situ formation of a valve |
US20100249920A1 (en) | 2007-01-08 | 2010-09-30 | Millipede Llc | Reconfiguring heart features |
US20080167705A1 (en) | 2007-01-10 | 2008-07-10 | Cook Incorporated | Short wire stent delivery system with splittable outer sheath |
WO2008097589A1 (en) | 2007-02-05 | 2008-08-14 | Boston Scientific Limited | Percutaneous valve, system, and method |
EP3345572A1 (de) | 2007-02-14 | 2018-07-11 | Edwards Lifesciences Corporation | Naht und verfahren zur herzreparatur |
US8529431B2 (en) | 2007-02-14 | 2013-09-10 | Bfkw, Llc | Bariatric device and method |
WO2008103280A2 (en) | 2007-02-16 | 2008-08-28 | Medtronic, Inc. | Delivery systems and methods of implantation for replacement prosthetic heart valves |
US7753949B2 (en) | 2007-02-23 | 2010-07-13 | The Trustees Of The University Of Pennsylvania | Valve prosthesis systems and methods |
US8070802B2 (en) | 2007-02-23 | 2011-12-06 | The Trustees Of The University Of Pennsylvania | Mitral valve system |
US20080208327A1 (en) | 2007-02-27 | 2008-08-28 | Rowe Stanton J | Method and apparatus for replacing a prosthetic valve |
WO2008109087A1 (en) | 2007-03-05 | 2008-09-12 | C2M Medical, Inc. | Tack anchor systems, bone anchor systems,and method of use |
US8845723B2 (en) | 2007-03-13 | 2014-09-30 | Mitralign, Inc. | Systems and methods for introducing elements into tissue |
US8911461B2 (en) | 2007-03-13 | 2014-12-16 | Mitralign, Inc. | Suture cutter and method of cutting suture |
WO2008121380A1 (en) | 2007-03-31 | 2008-10-09 | Cook Incorporated | Medical device delivery system with sheath separation |
US7896915B2 (en) | 2007-04-13 | 2011-03-01 | Jenavalve Technology, Inc. | Medical device for treating a heart valve insufficiency |
US9387308B2 (en) | 2007-04-23 | 2016-07-12 | Cardioguidance Biomedical, Llc | Guidewire with adjustable stiffness |
US8273115B2 (en) | 2007-04-24 | 2012-09-25 | W. L. Gore & Associates, Inc. | Side branched endoluminal prostheses and methods of delivery thereof |
JP2010524651A (ja) | 2007-04-27 | 2010-07-22 | ボエッジ メディカル, インコーポレイテッド | 複雑な形状の操縦可能な組織可視化および操作カテーテル |
US8529620B2 (en) | 2007-05-01 | 2013-09-10 | Ottavio Alfieri | Inwardly-bowed tricuspid annuloplasty ring |
US8147504B2 (en) | 2007-05-05 | 2012-04-03 | Medtronic, Inc. | Apparatus and methods for delivering fasteners during valve replacement |
US7931660B2 (en) | 2007-05-10 | 2011-04-26 | Tyco Healthcare Group Lp | Powered tacker instrument |
JP5424063B2 (ja) | 2007-05-11 | 2014-02-26 | クック・メディカル・テクノロジーズ・リミテッド・ライアビリティ・カンパニー | ステントグラフトを一時的に縮径するための拘束構造および方法 |
GR20070100291A (el) | 2007-05-14 | 2008-12-19 | Κωνστατινος Σπαργιας | Μπαλονια βαλβιδοπλαστικης για την στενωση αορτικης βαλβιδας που φερουν επιστρωση εκλυομενης φαρμακευτικης ουσιας η οποια επιδρα προληπτικα κατα της επαναστενωσης |
EP2659861B1 (de) | 2007-05-15 | 2019-03-13 | JenaValve Technology, Inc. | Griff zur Manipulation einer Katheterspitze, Kathetersystem und medizinisches Einführsystem zum Einführen eines selbstexpandierbaren Herzklappenstents |
US8740937B2 (en) | 2007-05-31 | 2014-06-03 | Cook Medical Technologies Llc | Suture lock |
US20090112159A1 (en) | 2007-10-31 | 2009-04-30 | David Slattery | Delivery System With Profiled Sheath Having Balloon-Oriented Position |
US8512398B2 (en) | 2007-06-26 | 2013-08-20 | St. Jude Medical, Inc. | Apparatus and method for implanting collapsible/expandable prosthetic heart valves |
US9814611B2 (en) | 2007-07-31 | 2017-11-14 | Edwards Lifesciences Cardiaq Llc | Actively controllable stent, stent graft, heart valve and method of controlling same |
US9566178B2 (en) | 2010-06-24 | 2017-02-14 | Edwards Lifesciences Cardiaq Llc | Actively controllable stent, stent graft, heart valve and method of controlling same |
US8252035B2 (en) | 2007-08-01 | 2012-08-28 | Cappella, Inc. | Device delivery system with two stage withdrawal |
CA2978267A1 (en) | 2007-08-23 | 2009-02-23 | Dfm, Llc | Translumenally implantable heart valve with formed in place support |
BRPI0815751A2 (pt) | 2007-08-24 | 2015-02-18 | St Jude Medical | Válvula aórtica protética. |
DE102007043830A1 (de) | 2007-09-13 | 2009-04-02 | Lozonschi, Lucian, Madison | Herzklappenstent |
US20120150218A1 (en) | 2007-09-13 | 2012-06-14 | Robert Tyler Sandgren | Medical device for occluding a heart defect and a method of manufacturing the same |
US8066755B2 (en) | 2007-09-26 | 2011-11-29 | Trivascular, Inc. | System and method of pivoted stent deployment |
EP2190385B8 (de) | 2007-09-26 | 2017-06-07 | St. Jude Medical, LLC | Faltbare herzklappenprothesen |
WO2009045334A1 (en) | 2007-09-28 | 2009-04-09 | St. Jude Medical, Inc. | Collapsible/expandable prosthetic heart valves with native calcified leaflet retention features |
US20090088837A1 (en) | 2007-09-28 | 2009-04-02 | The Cleveland Clinic Foundation | Prosthetic chordae assembly and method of use |
US8454686B2 (en) | 2007-09-28 | 2013-06-04 | St. Jude Medical, Inc. | Two-stage collapsible/expandable prosthetic heart valves and anchoring systems |
CA2702672C (en) | 2007-10-15 | 2016-03-15 | Edwards Lifesciences Corporation | Transcatheter heart valve with micro-anchors |
CA2702615C (en) | 2007-10-19 | 2017-06-06 | Guided Delivery Systems, Inc. | Systems and methods for cardiac remodeling |
WO2009052438A2 (en) | 2007-10-19 | 2009-04-23 | Guided Delivery Systems Inc. | Devices for termination of tethers |
US20090105816A1 (en) | 2007-10-19 | 2009-04-23 | Olsen Daniel H | System using a helical retainer in the direct plication annuloplasty treatment of mitral valve regurgitation |
US8647381B2 (en) | 2007-10-25 | 2014-02-11 | Symetis Sa | Stents, valved-stents, and methods and systems for delivery thereof |
US8715337B2 (en) | 2007-11-09 | 2014-05-06 | Cook Medical Technologies Llc | Aortic valve stent graft |
US8057532B2 (en) | 2007-11-28 | 2011-11-15 | Cook Medical Technologies Llc | Implantable frame and valve design |
DK3646822T3 (da) | 2007-12-14 | 2021-09-06 | Edwards Lifesciences Corp | Bladfastgørelsesramme til en proteseklap |
EP2072027B1 (de) | 2007-12-21 | 2020-06-17 | Medtentia International Ltd Oy | präannuloplastievorrichtung und verfahren |
US8277501B2 (en) | 2007-12-21 | 2012-10-02 | Boston Scientific Scimed, Inc. | Bi-stable bifurcated stent petal geometry |
WO2009086535A2 (en) | 2007-12-27 | 2009-07-09 | The Trustees Of Columbia University In The City Of New York | Systems and methods for forming patterned extracellular matrix materials |
FR2925838A1 (fr) | 2007-12-28 | 2009-07-03 | Univ Franche Comte Etablisseme | Ancillaire automatise d'insertion et de fixation par agrafage d'un corps annulaire, notamment d'une prothese, sur un volume annulaire resilient |
EP2240121B1 (de) | 2008-01-16 | 2019-05-22 | St. Jude Medical, Inc. | System zur ausgabe und entnahme falt- und dehnbarer herzklappenprothesen |
WO2009090564A2 (en) | 2008-01-16 | 2009-07-23 | Simcha Milo | Adjustable annuloplasty rings |
WO2009094373A1 (en) | 2008-01-22 | 2009-07-30 | Cook Incorporated | Valve frame |
WO2009094585A2 (en) | 2008-01-24 | 2009-07-30 | Coherex Medical, Inc. | Methods and apparatus for reducing valve prolaspe |
US8157853B2 (en) | 2008-01-24 | 2012-04-17 | Medtronic, Inc. | Delivery systems and methods of implantation for prosthetic heart valves |
WO2009100242A2 (en) | 2008-02-06 | 2009-08-13 | Guided Delivery Systems, Inc. | Multi-window guide tunnel |
JP2011512948A (ja) | 2008-02-25 | 2011-04-28 | メドトロニック カルディオ ヴァスキュラー インコーポレイテッド | 漏斗部整復器具 |
US8728097B1 (en) | 2008-02-26 | 2014-05-20 | Mitralign, Inc. | Tissue plication devices and methods for their use |
US9241792B2 (en) | 2008-02-29 | 2016-01-26 | Edwards Lifesciences Corporation | Two-step heart valve implantation |
WO2009114316A2 (en) | 2008-03-03 | 2009-09-17 | Alaska Hand Research, Llc | Cannulated anchor and system |
US8177836B2 (en) | 2008-03-10 | 2012-05-15 | Medtronic, Inc. | Apparatus and methods for minimally invasive valve repair |
US8382829B1 (en) | 2008-03-10 | 2013-02-26 | Mitralign, Inc. | Method to reduce mitral regurgitation by cinching the commissure of the mitral valve |
US8313525B2 (en) | 2008-03-18 | 2012-11-20 | Medtronic Ventor Technologies, Ltd. | Valve suturing and implantation procedures |
WO2009120764A2 (en) | 2008-03-25 | 2009-10-01 | Ellipse Technologies, Inc. | Systems and methods for adjusting an annuloplasty ring with an integrated magnetic drive |
EP2273948A4 (de) | 2008-04-03 | 2014-01-01 | Gardia Medical Ltd | Abgabekatheter mit halteschleuse und verfahren zur ablage von medizinischen vorrichtungen in einem körperlumen |
US8262725B2 (en) | 2008-04-16 | 2012-09-11 | Cardiovascular Technologies, Llc | Transvalvular intraannular band for valve repair |
US20100121437A1 (en) | 2008-04-16 | 2010-05-13 | Cardiovascular Technologies, Llc | Transvalvular intraannular band and chordae cutting for ischemic and dilated cardiomyopathy |
AU2009239670B2 (en) | 2008-04-21 | 2013-11-14 | Quickring Medical Technologies Ltd. | Surgical stapling systems |
US20090264859A1 (en) | 2008-04-21 | 2009-10-22 | Medtronic Vascular, Inc. | Catheter Having a Selectively Expandable Distal Tip |
BRPI0911351B8 (pt) | 2008-04-23 | 2021-06-22 | Medtronic Inc | estrutura de stent para uma válvula cardíaca protética, e, prótese de válvula cardíaca |
US8696743B2 (en) | 2008-04-23 | 2014-04-15 | Medtronic, Inc. | Tissue attachment devices and methods for prosthetic heart valves |
DK3967274T3 (da) | 2008-04-23 | 2022-10-03 | Medtronic Inc | Hjerteklapanordninger med stent |
US8136218B2 (en) | 2008-04-29 | 2012-03-20 | Medtronic, Inc. | Prosthetic heart valve, prosthetic heart valve assembly and method for making same |
US20090276040A1 (en) | 2008-05-01 | 2009-11-05 | Edwards Lifesciences Corporation | Device and method for replacing mitral valve |
US9061119B2 (en) | 2008-05-09 | 2015-06-23 | Edwards Lifesciences Corporation | Low profile delivery system for transcatheter heart valve |
US8152844B2 (en) | 2008-05-09 | 2012-04-10 | Edwards Lifesciences Corporation | Quick-release annuloplasty ring holder |
WO2009140298A2 (en) | 2008-05-12 | 2009-11-19 | Wright John T M | Device and method for the surgical treatment of ischemic mitral regurgitation |
US20090287304A1 (en) | 2008-05-13 | 2009-11-19 | Kardium Inc. | Medical Device for Constricting Tissue or a Bodily Orifice, for example a mitral valve |
GB0809357D0 (en) | 2008-05-22 | 2008-07-02 | Punjabi Prakash | Heart valve repair device |
US8317806B2 (en) | 2008-05-30 | 2012-11-27 | Ethicon Endo-Surgery, Inc. | Endoscopic suturing tension controlling and indication devices |
EP3476368B1 (de) | 2008-06-06 | 2020-01-01 | Edwards Lifesciences Corporation | Transkatheterherzklappe mit niedrigem profil |
US8591460B2 (en) | 2008-06-13 | 2013-11-26 | Cardiosolutions, Inc. | Steerable catheter and dilator and system and method for implanting a heart implant |
EP2296744B1 (de) | 2008-06-16 | 2019-07-31 | Valtech Cardio, Ltd. | Annuloplastievorrichtungen |
JP2011524776A (ja) | 2008-06-20 | 2011-09-08 | ヴィセラ・バイオメディカル・リミテッド | 食道弁 |
US8323335B2 (en) | 2008-06-20 | 2012-12-04 | Edwards Lifesciences Corporation | Retaining mechanisms for prosthetic valves and methods for using |
US8087142B2 (en) | 2008-07-02 | 2012-01-03 | Easylap Ltd. | Pivoting tacker |
EP2321069B1 (de) | 2008-07-04 | 2017-11-01 | Tata Steel UK Limited | Verfahren zur beschichtung eines stahlsubstrats und beschichtetes stahlsubstrat |
US20100010538A1 (en) | 2008-07-11 | 2010-01-14 | Maquet Cardiovascular Llc | Reshaping the mitral valve of a heart |
EP2331016B8 (de) | 2008-07-15 | 2020-06-03 | St. Jude Medical, LLC | Axiale verankerung von kollabierbaren und reexpandierbaren herzklappenprothesen für verschiedene krankheiten |
EP3838221A1 (de) | 2008-07-15 | 2021-06-23 | St. Jude Medical, LLC | Entwürfe für eine zusammenlegbare und auseinanderziehbare manschette für eine herzklappenprothese und zugehörige technologische anwendungen |
CN102119013B (zh) | 2008-07-17 | 2014-12-03 | Nvt股份公司 | 心脏瓣膜假体系统 |
CN104771248B (zh) | 2008-07-21 | 2018-06-05 | 爱德华兹生命科学卡迪尔克有限责任公司 | 可重新定位的腔内支撑结构及其应用 |
US20100023118A1 (en) | 2008-07-24 | 2010-01-28 | Edwards Lifesciences Corporation | Method and apparatus for repairing or replacing chordae tendinae |
BRPI0916696A2 (pt) | 2008-07-29 | 2015-11-17 | St Jude Medical Cardiology Div | método e sistema para ajuste a longo prazo de um dispositivo de implante |
US8337390B2 (en) | 2008-07-30 | 2012-12-25 | Cube S.R.L. | Intracardiac device for restoring the functional elasticity of the cardiac structures, holding tool for the intracardiac device, and method for implantation of the intracardiac device in the heart |
US8778016B2 (en) | 2008-08-14 | 2014-07-15 | Edwards Lifesciences Corporation | Method and apparatus for repairing or replacing chordae tendinae |
US8652202B2 (en) | 2008-08-22 | 2014-02-18 | Edwards Lifesciences Corporation | Prosthetic heart valve and delivery apparatus |
AU2009288697B2 (en) | 2008-09-05 | 2013-06-20 | Cook Medical Technologies Llc | Apparatus and methods for improved stent deployment |
US8777990B2 (en) | 2008-09-08 | 2014-07-15 | Howmedica Osteonics Corp. | Knotless suture anchor for soft tissue repair and method of use |
US9408649B2 (en) | 2008-09-11 | 2016-08-09 | Innovasis, Inc. | Radiolucent screw with radiopaque marker |
US8945211B2 (en) | 2008-09-12 | 2015-02-03 | Mitralign, Inc. | Tissue plication device and method for its use |
US8721714B2 (en) | 2008-09-17 | 2014-05-13 | Medtronic Corevalve Llc | Delivery system for deployment of medical devices |
US9314335B2 (en) | 2008-09-19 | 2016-04-19 | Edwards Lifesciences Corporation | Prosthetic heart valve configured to receive a percutaneous prosthetic heart valve implantation |
US8287591B2 (en) | 2008-09-19 | 2012-10-16 | Edwards Lifesciences Corporation | Transformable annuloplasty ring configured to receive a percutaneous prosthetic heart valve implantation |
CN102224503A (zh) | 2008-09-24 | 2011-10-19 | 比安卡医疗有限公司 | 用于评估和干预的生活质量参数的无接触和最小接触监控 |
CA2749026C (en) | 2008-09-29 | 2018-01-09 | Impala, Inc. | Heart valve |
CA2739275C (en) | 2008-10-01 | 2017-01-17 | Impala, Inc. | Delivery system for vascular implant |
WO2010042857A1 (en) | 2008-10-10 | 2010-04-15 | Guided Delivery Systems Inc. | Tether tensioning devices and related methods |
WO2010042950A2 (en) | 2008-10-10 | 2010-04-15 | Sadra Medical, Inc. | Medical devices and delivery systems for delivering medical devices |
CA2740233C (en) | 2008-10-10 | 2017-10-03 | Guided Delivery Systems, Inc. | Termination devices and related methods |
US8137398B2 (en) | 2008-10-13 | 2012-03-20 | Medtronic Ventor Technologies Ltd | Prosthetic valve having tapered tip when compressed for delivery |
US8986361B2 (en) | 2008-10-17 | 2015-03-24 | Medtronic Corevalve, Inc. | Delivery system for deployment of medical devices |
US8449625B2 (en) | 2009-10-27 | 2013-05-28 | Edwards Lifesciences Corporation | Methods of measuring heart valve annuluses for valve replacement |
US8696717B2 (en) | 2008-11-05 | 2014-04-15 | K2M, Inc. | Multi-planar, taper lock screw with additional lock |
EP2358297B1 (de) | 2008-11-21 | 2019-09-11 | Percutaneous Cardiovascular Solutions Pty Limited | Herzklappenprothese |
DE102008058894B3 (de) | 2008-11-26 | 2010-06-17 | Vimecon Gmbh | Laserapplikator |
JP5530455B2 (ja) | 2008-12-04 | 2014-06-25 | ジョージア テック リサーチ コーポレーション | 低侵襲心臓弁処置のための装置 |
EP2196478A1 (de) | 2008-12-12 | 2010-06-16 | EMPA Eidgenössische Materialprüfungs- und Forschungsanstalt | Oberflächenmodifizierte Cellulosenanofibrillen |
WO2010070788A1 (ja) | 2008-12-19 | 2010-06-24 | パナソニック株式会社 | 外装部品およびその製造方法ならびに電子機器 |
US8308798B2 (en) | 2008-12-19 | 2012-11-13 | Edwards Lifesciences Corporation | Quick-connect prosthetic heart valve and methods |
US9011530B2 (en) | 2008-12-22 | 2015-04-21 | Valtech Cardio, Ltd. | Partially-adjustable annuloplasty structure |
US8715342B2 (en) | 2009-05-07 | 2014-05-06 | Valtech Cardio, Ltd. | Annuloplasty ring with intra-ring anchoring |
US8241351B2 (en) | 2008-12-22 | 2012-08-14 | Valtech Cardio, Ltd. | Adjustable partial annuloplasty ring and mechanism therefor |
US8940044B2 (en) | 2011-06-23 | 2015-01-27 | Valtech Cardio, Ltd. | Closure element for use with an annuloplasty structure |
US8808368B2 (en) | 2008-12-22 | 2014-08-19 | Valtech Cardio, Ltd. | Implantation of repair chords in the heart |
US10517719B2 (en) | 2008-12-22 | 2019-12-31 | Valtech Cardio, Ltd. | Implantation of repair devices in the heart |
US8911494B2 (en) | 2009-05-04 | 2014-12-16 | Valtech Cardio, Ltd. | Deployment techniques for annuloplasty ring |
US8926697B2 (en) | 2011-06-23 | 2015-01-06 | Valtech Cardio, Ltd. | Closed band for percutaneous annuloplasty |
US8323312B2 (en) | 2008-12-22 | 2012-12-04 | Abbott Laboratories | Closure device |
ES2873182T3 (es) | 2008-12-22 | 2021-11-03 | Valtech Cardio Ltd | Dispositivos de anuloplastia ajustables |
US8147542B2 (en) | 2008-12-22 | 2012-04-03 | Valtech Cardio, Ltd. | Adjustable repair chords and spool mechanism therefor |
EP2381895B1 (de) | 2008-12-31 | 2021-07-07 | Medtronic, Inc. | Halbstarrer annuloplastiering und band und methode zur herstellung eines annuloplastierings |
US20110011917A1 (en) | 2008-12-31 | 2011-01-20 | Hansen Medical, Inc. | Methods, devices, and kits for treating valve prolapse |
EP2393451B1 (de) | 2009-01-07 | 2017-04-26 | Cook Medical Technologies LLC | Implantierbare klappenprothese mit unabhängigen rahmenelementen |
US20100174363A1 (en) | 2009-01-07 | 2010-07-08 | Endovalve, Inc. | One Piece Prosthetic Valve Support Structure and Related Assemblies |
US8795328B2 (en) | 2009-01-08 | 2014-08-05 | Coherex Medical, Inc. | Medical device for modification of left atrial appendage and related systems and methods |
US9681950B2 (en) | 2009-01-12 | 2017-06-20 | Valve Medical Ltd. | System and method for placing a percutaneous valve device |
US8998982B2 (en) | 2009-01-12 | 2015-04-07 | Valve Medical Ltd. | Method and apparatus for fine adjustment of a percutaneous valve structure |
US9204965B2 (en) | 2009-01-14 | 2015-12-08 | Lc Therapeutics, Inc. | Synthetic chord |
WO2010085456A1 (en) | 2009-01-20 | 2010-07-29 | Guided Delivery Systems Inc. | Anchor deployment devices and related methods |
AU2010206732A1 (en) | 2009-01-22 | 2011-08-25 | St. Jude Medical, Cardiology Division, Inc. | Post-operative adjustment tool, minimally invasive attachment apparatus, and adjustable tricuspid ring |
US8784484B2 (en) | 2009-02-06 | 2014-07-22 | St. Jude Medical, Inc. | Adjustable annuloplasty ring support |
WO2010091383A2 (en) | 2009-02-09 | 2010-08-12 | St. Jude Medical | Inflatable minimally invasive system for delivering and securing an annular implant |
EP2395944B1 (de) | 2009-02-11 | 2020-09-23 | Georg Lutter | Kathetersystem zur Rekonstruktion einer anatomischen Struktur |
CN102438530A (zh) | 2009-02-16 | 2012-05-02 | 泰根尼克斯股份有限公司 | 活检装置 |
US8353956B2 (en) | 2009-02-17 | 2013-01-15 | Valtech Cardio, Ltd. | Actively-engageable movement-restriction mechanism for use with an annuloplasty structure |
US20110144703A1 (en) | 2009-02-24 | 2011-06-16 | Krause William R | Flexible Screw |
US20100217382A1 (en) | 2009-02-25 | 2010-08-26 | Edwards Lifesciences | Mitral valve replacement with atrial anchoring |
JP5659168B2 (ja) | 2009-02-27 | 2015-01-28 | セント・ジュード・メディカル,インコーポレイテッド | 折畳み可能な人工心臓弁用ステント特徴部 |
US8021420B2 (en) | 2009-03-12 | 2011-09-20 | Medtronic Vascular, Inc. | Prosthetic valve delivery system |
JP2012520716A (ja) | 2009-03-17 | 2012-09-10 | ミトラシスト メディカル リミテッド | 折りたためる弁を持つ人工弁及びその送出方法 |
US8052741B2 (en) | 2009-03-23 | 2011-11-08 | Medtronic Vascular, Inc. | Branch vessel prosthesis with a roll-up sealing assembly |
CN101919753A (zh) | 2009-03-30 | 2010-12-22 | 卡迪万蒂奇医药公司 | 人工主动脉瓣膜或二尖瓣膜的无缝合移植方法和装置 |
US9980818B2 (en) | 2009-03-31 | 2018-05-29 | Edwards Lifesciences Corporation | Prosthetic heart valve system with positioning markers |
US8986370B2 (en) | 2009-04-10 | 2015-03-24 | Lon Sutherland ANNEST | Implantable scaffolding containing an orifice for use with a prosthetic or bio-prosthetic valve |
US20100262233A1 (en) | 2009-04-12 | 2010-10-14 | Texas Tech University System | Mitral Valve Coaptation Plate For Mitral Valve Regurgitation |
WO2010121076A2 (en) | 2009-04-15 | 2010-10-21 | Cardiaq Valve Technologies, Inc. | Vascular implant and delivery system |
EP2429455B8 (de) | 2009-04-29 | 2021-12-15 | Edwards Lifesciences Corporation | Vorrichtung für den ersatz einer defekten herzklappe |
US9968452B2 (en) | 2009-05-04 | 2018-05-15 | Valtech Cardio, Ltd. | Annuloplasty ring delivery cathethers |
WO2010128501A1 (en) | 2009-05-04 | 2010-11-11 | V-Wave Ltd. | Device and method for regulating pressure in a heart chamber |
WO2010129900A1 (en) | 2009-05-07 | 2010-11-11 | Georgia Tech Research Corporation | Implantable prosthetic vascular valves |
US20100286628A1 (en) | 2009-05-07 | 2010-11-11 | Rainbow Medical Ltd | Gastric anchor |
US8523881B2 (en) | 2010-07-26 | 2013-09-03 | Valtech Cardio, Ltd. | Multiple anchor delivery tool |
US8075611B2 (en) | 2009-06-02 | 2011-12-13 | Medtronic, Inc. | Stented prosthetic heart valves |
US20120083832A1 (en) | 2009-06-03 | 2012-04-05 | Symetis Sa | Closure device and methods and systems for using same |
EP2445417A2 (de) | 2009-06-26 | 2012-05-02 | QuickRing Medical Technologies Ltd. | Chirurgisches klammergerät |
US8348998B2 (en) | 2009-06-26 | 2013-01-08 | Edwards Lifesciences Corporation | Unitary quick connect prosthetic heart valve and deployment system and methods |
US8475522B2 (en) | 2009-07-14 | 2013-07-02 | Edwards Lifesciences Corporation | Transapical delivery system for heart valves |
US20110022165A1 (en) | 2009-07-23 | 2011-01-27 | Edwards Lifesciences Corporation | Introducer for prosthetic heart valve |
US8845722B2 (en) | 2009-08-03 | 2014-09-30 | Shlomo Gabbay | Heart valve prosthesis and method of implantation thereof |
US8801706B2 (en) | 2009-08-27 | 2014-08-12 | Medtronic, Inc. | Paravalvular leak closure devices and methods |
CN102762170B (zh) | 2009-08-28 | 2016-02-10 | 美敦力3F医疗有限公司 | 皱缩装置 |
KR101116867B1 (ko) | 2009-08-28 | 2012-03-06 | 김준홍 | 관상정맥동과 삼천판막의 조직보호기구, 매듭 전달 기구 및 이들을 포함하는 승모판막 서클라지 시술용 장치 |
US9265596B2 (en) | 2009-09-11 | 2016-02-23 | Gi Dynamics, Inc. | Anchors with open heads |
EP2477555B1 (de) | 2009-09-15 | 2013-12-25 | Evalve, Inc. | Vorrichtung zur reparatur von herzklappen |
US8459302B2 (en) | 2009-09-21 | 2013-06-11 | Gulf Sea Ventures LLC | Fluid-directing multiport rotary valve |
US9730790B2 (en) | 2009-09-29 | 2017-08-15 | Edwards Lifesciences Cardiaq Llc | Replacement valve and method |
US20110077730A1 (en) | 2009-09-30 | 2011-03-31 | Fenster Michael S | Bifurcated balloon stent |
US20110082538A1 (en) | 2009-10-01 | 2011-04-07 | Jonathan Dahlgren | Medical device, kit and method for constricting tissue or a bodily orifice, for example, a mitral valve |
US20190060070A1 (en) | 2009-10-06 | 2019-02-28 | Adam Groothuis | Systems and methods for treating lumenal valves |
WO2011044486A1 (en) | 2009-10-09 | 2011-04-14 | Boston Scientific Scimed, Inc. | Stomach bypass for the treatment of obesity |
US20110093002A1 (en) | 2009-10-20 | 2011-04-21 | Wilson-Cook Medical Inc. | Stent-within-stent arrangements |
JP5875986B2 (ja) | 2009-10-26 | 2016-03-02 | カーディオキネティックス・インコーポレイテッドCardiokinetix, Inc. | 心室容積縮小 |
US8690939B2 (en) | 2009-10-29 | 2014-04-08 | Valtech Cardio, Ltd. | Method for guide-wire based advancement of a rotation assembly |
US8277502B2 (en) | 2009-10-29 | 2012-10-02 | Valtech Cardio, Ltd. | Tissue anchor for annuloplasty device |
US9011520B2 (en) | 2009-10-29 | 2015-04-21 | Valtech Cardio, Ltd. | Tissue anchor for annuloplasty device |
US9289291B2 (en) | 2009-11-05 | 2016-03-22 | The Trustees Of The University Of Pennsylvania | Valve prosthesis |
DE102009046769A1 (de) | 2009-11-17 | 2011-05-19 | Robert Bosch Gmbh | Abgasnachbehandlungseinrichtung |
US8734467B2 (en) | 2009-12-02 | 2014-05-27 | Valtech Cardio, Ltd. | Delivery tool for implantation of spool assembly coupled to a helical anchor |
US8449599B2 (en) | 2009-12-04 | 2013-05-28 | Edwards Lifesciences Corporation | Prosthetic valve for replacing mitral valve |
US20130190861A1 (en) | 2012-01-23 | 2013-07-25 | Tendyne Holdings, Inc. | Prosthetic Valve for Replacing Mitral Valve |
WO2011072084A2 (en) | 2009-12-08 | 2011-06-16 | Avalon Medical Ltd. | Device and system for transcatheter mitral valve replacement |
US8870950B2 (en) | 2009-12-08 | 2014-10-28 | Mitral Tech Ltd. | Rotation-based anchoring of an implant |
EP2512375B1 (de) | 2009-12-15 | 2016-12-07 | Edwards Lifesciences Corporation | Expansionsvorrichtung zur behandlung von gefässdurchgängen |
US8876800B2 (en) | 2009-12-18 | 2014-11-04 | Vysera Biomedical Limited | Urological device |
US20110230961A1 (en) | 2010-01-05 | 2011-09-22 | Micardia Corporation | Dynamically adjustable annuloplasty ring and papillary muscle repositioning suture |
US9504562B2 (en) | 2010-01-12 | 2016-11-29 | Valve Medical Ltd. | Self-assembling modular percutaneous valve and methods of folding, assembly and delivery |
US8961596B2 (en) | 2010-01-22 | 2015-02-24 | 4Tech Inc. | Method and apparatus for tricuspid valve repair using tension |
US8475525B2 (en) | 2010-01-22 | 2013-07-02 | 4Tech Inc. | Tricuspid valve repair using tension |
GB201001075D0 (en) | 2010-01-22 | 2010-03-10 | Cyclacel Ltd | Crystalline forms |
CN102985031B (zh) | 2010-02-03 | 2015-09-30 | 美敦力Gbi有限公司 | 半挠性瓣环成形术环 |
US9107749B2 (en) | 2010-02-03 | 2015-08-18 | Edwards Lifesciences Corporation | Methods for treating a heart |
US8926693B2 (en) | 2010-02-17 | 2015-01-06 | Medtronic, Inc. | Heart valve delivery catheter with safety button |
US20110208293A1 (en) | 2010-02-23 | 2011-08-25 | Medtronic, Inc. | Catheter-Based Heart Valve Therapy System with Sizing Balloon |
US9522062B2 (en) | 2010-02-24 | 2016-12-20 | Medtronic Ventor Technologies, Ltd. | Mitral prosthesis and methods for implantation |
US9072603B2 (en) | 2010-02-24 | 2015-07-07 | Medtronic Ventor Technologies, Ltd. | Mitral prosthesis and methods for implantation |
US9226826B2 (en) | 2010-02-24 | 2016-01-05 | Medtronic, Inc. | Transcatheter valve structure and methods for valve delivery |
US8545552B2 (en) | 2010-02-26 | 2013-10-01 | Silk Road Medical, Inc. | Systems and methods for transcatheter aortic valve treatment |
CN102869320B (zh) | 2010-03-01 | 2016-10-12 | 科利柏心脏瓣膜有限责任公司 | 可经皮输送的心脏瓣膜及相关制备方法 |
US8795354B2 (en) | 2010-03-05 | 2014-08-05 | Edwards Lifesciences Corporation | Low-profile heart valve and delivery system |
ES2922283T3 (es) | 2010-03-05 | 2022-09-12 | Edwards Lifesciences Corp | Mecanismos de retención para válvulas protésicas |
US20110224785A1 (en) | 2010-03-10 | 2011-09-15 | Hacohen Gil | Prosthetic mitral valve with tissue anchors |
US20110238094A1 (en) | 2010-03-25 | 2011-09-29 | Thomas Jonathan D | Hernia Patch |
US8992599B2 (en) | 2010-03-26 | 2015-03-31 | Thubrikar Aortic Valve, Inc. | Valve component, frame component and prosthetic valve device including the same for implantation in a body lumen |
US9320597B2 (en) | 2010-03-30 | 2016-04-26 | Medtronic, Inc. | Transcatheter prosthetic heart valve delivery system with recapturing feature and method |
US8652204B2 (en) | 2010-04-01 | 2014-02-18 | Medtronic, Inc. | Transcatheter valve with torsion spring fixation and related systems and methods |
US8491650B2 (en) | 2010-04-08 | 2013-07-23 | Medtronic, Inc. | Transcatheter prosthetic heart valve delivery system and method with stretchable stability tube |
US8926692B2 (en) | 2010-04-09 | 2015-01-06 | Medtronic, Inc. | Transcatheter prosthetic heart valve delivery device with partial deployment and release features and methods |
US8512400B2 (en) | 2010-04-09 | 2013-08-20 | Medtronic, Inc. | Transcatheter heart valve delivery system with reduced area moment of inertia |
US20110251676A1 (en) | 2010-04-12 | 2011-10-13 | Medtronic Vascular, Inc. | Sheath for Controlled Delivery of a Heart Valve Prosthesis |
US8512401B2 (en) | 2010-04-12 | 2013-08-20 | Medtronic, Inc. | Transcatheter prosthetic heart valve delivery system with funnel recapturing feature and method |
US8579963B2 (en) | 2010-04-13 | 2013-11-12 | Medtronic, Inc. | Transcatheter prosthetic heart valve delivery device with stability tube and method |
US8357195B2 (en) | 2010-04-15 | 2013-01-22 | Medtronic, Inc. | Catheter based annuloplasty system and method |
US20110257721A1 (en) | 2010-04-15 | 2011-10-20 | Medtronic, Inc. | Prosthetic Heart Valves and Delivery Methods |
EP3858293A1 (de) | 2010-04-21 | 2021-08-04 | Medtronic, Inc. | Prothesenklappe mit dichtungselementen |
US8623075B2 (en) | 2010-04-21 | 2014-01-07 | Medtronic, Inc. | Transcatheter prosthetic heart valve delivery system and method with controlled expansion of prosthetic heart valve |
US8876892B2 (en) | 2010-04-21 | 2014-11-04 | Medtronic, Inc. | Prosthetic heart valve delivery system with spacing |
US8740976B2 (en) | 2010-04-21 | 2014-06-03 | Medtronic, Inc. | Transcatheter prosthetic heart valve delivery system with flush report |
EP2560589B1 (de) | 2010-04-23 | 2018-06-06 | Medtronic, Inc. | Freisetzungssysteme für herzklappenprothesen |
US8623079B2 (en) | 2010-04-23 | 2014-01-07 | Medtronic, Inc. | Stents for prosthetic heart valves |
US8568474B2 (en) | 2010-04-26 | 2013-10-29 | Medtronic, Inc. | Transcatheter prosthetic heart valve post-dilatation remodeling devices and methods |
EP2563278B1 (de) | 2010-04-27 | 2018-07-11 | Medtronic, Inc. | Vorrichtung zur transkatheter-freisetzung einer herzklappenprothese mit vorgespannten lösevorrichtungen |
US8876893B2 (en) | 2010-04-27 | 2014-11-04 | Medtronic, Inc. | Transcatheter prosthetic heart valve delivery device with passive trigger release |
US9795482B2 (en) | 2010-04-27 | 2017-10-24 | Medtronic, Inc. | Prosthetic heart valve devices and methods of valve repair |
US8974475B2 (en) | 2010-04-30 | 2015-03-10 | Medtronic, Inc. | Methods and devices for cardiac valve repair or replacement |
US8579964B2 (en) | 2010-05-05 | 2013-11-12 | Neovasc Inc. | Transcatheter mitral valve prosthesis |
AU2011250971B2 (en) | 2010-05-10 | 2015-05-07 | Hlt, Inc. | Stentless support structure |
US9554901B2 (en) | 2010-05-12 | 2017-01-31 | Edwards Lifesciences Corporation | Low gradient prosthetic heart valve |
US20110288435A1 (en) | 2010-05-19 | 2011-11-24 | George Michael Christy | Tactile sensory testing instrument |
US9433501B2 (en) | 2010-05-19 | 2016-09-06 | Direct Flow Medical, Inc. | Inflation media for implants |
US9603708B2 (en) | 2010-05-19 | 2017-03-28 | Dfm, Llc | Low crossing profile delivery catheter for cardiovascular prosthetic implant |
US10856978B2 (en) | 2010-05-20 | 2020-12-08 | Jenavalve Technology, Inc. | Catheter system |
US8790394B2 (en) | 2010-05-24 | 2014-07-29 | Valtech Cardio, Ltd. | Adjustable artificial chordeae tendineae with suture loops |
WO2011147849A1 (en) | 2010-05-25 | 2011-12-01 | Jenavalve Technology Inc. | Prosthetic heart valve and transcatheter delivered endoprosthesis comprising a prosthetic heart valve and a stent |
US9023095B2 (en) | 2010-05-27 | 2015-05-05 | Idev Technologies, Inc. | Stent delivery system with pusher assembly |
US9561102B2 (en) | 2010-06-02 | 2017-02-07 | Medtronic, Inc. | Transcatheter delivery system and method with controlled expansion and contraction of prosthetic heart valve |
EP2575685B1 (de) | 2010-06-07 | 2019-02-13 | Valtech Cardio, Ltd. | Vorrichtung für führungsdraht-basierte weiterentwicklung einer rotationsanordnung |
US9301864B2 (en) | 2010-06-08 | 2016-04-05 | Veniti, Inc. | Bi-directional stent delivery system |
US20130030522A1 (en) | 2010-06-16 | 2013-01-31 | Rowe Stanton J | Devices and methods for heart treatments |
JP6125999B2 (ja) | 2010-06-21 | 2017-05-10 | カルディアック バルブ テクノロジーズ,インコーポレーテッド | 人工心臓弁 |
US8408214B2 (en) | 2010-07-08 | 2013-04-02 | Benjamin Spenser | Method for implanting prosthetic valve |
US9326852B2 (en) | 2010-07-08 | 2016-05-03 | Benjamin Spenser | Method for implanting prosthetic valve |
US9095277B2 (en) | 2010-07-09 | 2015-08-04 | Mitralign, Inc. | Delivery catheter with forward-looking ultrasound imaging |
US8657872B2 (en) | 2010-07-19 | 2014-02-25 | Jacques Seguin | Cardiac valve repair system and methods of use |
US9132009B2 (en) | 2010-07-21 | 2015-09-15 | Mitraltech Ltd. | Guide wires with commissural anchors to advance a prosthetic valve |
US9763657B2 (en) | 2010-07-21 | 2017-09-19 | Mitraltech Ltd. | Techniques for percutaneous mitral valve replacement and sealing |
US8992604B2 (en) | 2010-07-21 | 2015-03-31 | Mitraltech Ltd. | Techniques for percutaneous mitral valve replacement and sealing |
WO2012012761A2 (en) | 2010-07-23 | 2012-01-26 | Edwards Lifesciences Corporation | Retaining mechanisms for prosthetic valves |
WO2012019052A2 (en) | 2010-08-04 | 2012-02-09 | Micardia Corporation | Percutaneous transcatheter repair of heart valves |
EP2605726A4 (de) | 2010-08-17 | 2015-01-07 | Palmaz Scient Inc | Transluminale herz-kugelklappe und verfahren zu ihrem einsatz |
US9408694B2 (en) | 2010-08-17 | 2016-08-09 | St. Jude Medical, Inc. | Tip for medical implant delivery system |
CA2808830A1 (en) | 2010-08-23 | 2012-03-01 | Edwards Lifesciences Corporation | Color-coded prosthetic valve system and methods for using the same |
US20120053680A1 (en) | 2010-08-24 | 2012-03-01 | Bolling Steven F | Reconfiguring Heart Features |
US10105224B2 (en) | 2010-09-01 | 2018-10-23 | Mvalve Technologies Ltd. | Cardiac valve support structure |
JP5970458B2 (ja) | 2010-09-01 | 2016-08-17 | ムバルブ・テクノロジーズ・リミテッド | 心臓弁支持構造体 |
CN103118629A (zh) | 2010-09-01 | 2013-05-22 | 美敦力瓦斯科尔勒戈尔韦有限公司 | 假体瓣膜支承结构 |
US9861350B2 (en) | 2010-09-03 | 2018-01-09 | Ancora Heart, Inc. | Devices and methods for anchoring tissue |
CA2808673C (en) | 2010-09-10 | 2019-07-02 | Symetis Sa | Valve replacement devices, delivery device for a valve replacement device and method of production of a valve replacement device |
US10076327B2 (en) | 2010-09-14 | 2018-09-18 | Evalve, Inc. | Flexible actuator mandrel for tissue apposition systems |
EP2616006B1 (de) | 2010-09-17 | 2018-08-29 | St. Jude Medical, Cardiology Division, Inc. | Halterungen für transkatheter-herzklappenfreisetzungssysteme |
USD653341S1 (en) | 2010-09-20 | 2012-01-31 | St. Jude Medical, Inc. | Surgical stent |
USD652927S1 (en) | 2010-09-20 | 2012-01-24 | St. Jude Medical, Inc. | Surgical stent |
EP4176842A1 (de) | 2010-09-20 | 2023-05-10 | St. Jude Medical, Cardiology Division, Inc. | Klappensegelbefestigung in zusammenklappbaren prothesenklappen |
USD660433S1 (en) | 2010-09-20 | 2012-05-22 | St. Jude Medical, Inc. | Surgical stent assembly |
USD660967S1 (en) | 2010-09-20 | 2012-05-29 | St. Jude Medical, Inc. | Surgical stent |
EP3001978B2 (de) | 2010-09-23 | 2023-03-01 | Edwards Lifesciences CardiAQ LLC | Künstliche herzklappen sowie vorrichtungen und verfahren zu ihrem einsatz |
EP3111889B1 (de) | 2010-09-24 | 2019-11-13 | Symetis SA | Implantationssystem von transkatheter-aortenklappen |
US8845720B2 (en) * | 2010-09-27 | 2014-09-30 | Edwards Lifesciences Corporation | Prosthetic heart valve frame with flexible commissures |
CN111265338B (zh) * | 2010-10-05 | 2021-04-13 | 爱德华兹生命科学公司 | 人工心脏瓣膜 |
CN105380730B (zh) | 2010-10-05 | 2018-08-17 | 爱德华兹生命科学公司 | 人工心脏瓣膜 |
EP2629699B1 (de) | 2010-10-21 | 2017-01-04 | Medtronic, Inc. | Mitralbioprothese mit niedrigem ventrikulären profil |
US8968335B2 (en) | 2010-10-27 | 2015-03-03 | Mitralign, Inc. | Hand operated device for controlled deployment of a tissue anchor and method of using the same |
US9414944B2 (en) | 2010-11-11 | 2016-08-16 | W. L. Gore & Associates, Inc. | Deployment sleeve shortening mechanism |
US9468547B2 (en) | 2010-11-11 | 2016-10-18 | W. L. Gore & Associates, Inc. | Deployment of endoluminal devices |
US9005279B2 (en) | 2010-11-12 | 2015-04-14 | Shlomo Gabbay | Beating heart buttress and implantation method to prevent prolapse of a heart valve |
US9095466B2 (en) | 2010-11-16 | 2015-08-04 | W. L. Gore & Associates, Inc. | Apposition fiber for use in endoluminal deployment of expandable devices in tortuous anatomies |
US20120130475A1 (en) | 2010-11-16 | 2012-05-24 | Shaw Edward E | Sleeves for expandable medical devices |
US9675487B2 (en) | 2010-11-17 | 2017-06-13 | Cook Medical Technologies Llc | Prosthesis deployment system for vascular repair |
JP2014502859A (ja) | 2010-11-18 | 2014-02-06 | パビリオン・メディカル・イノベーションズ・リミテッド・ライアビリティ・カンパニー | 組織拘束装置及び使用方法 |
US9078750B2 (en) | 2010-11-30 | 2015-07-14 | Edwards Lifesciences Corporation | Ergonomic mitral heart valve holders |
US20120158021A1 (en) | 2010-12-19 | 2012-06-21 | Mitralign, Inc. | Steerable guide catheter having preformed curved shape |
US8657866B2 (en) | 2010-12-22 | 2014-02-25 | Cook Medical Technologies Llc | Emergency vascular repair prosthesis deployment system |
WO2012087842A1 (en) | 2010-12-23 | 2012-06-28 | The Foundry, Llc | System for mitral valve repair and replacement |
EP2663258B1 (de) | 2011-01-11 | 2018-11-21 | Hans Reiner Figulla | Klappenprothese zum ersatz einer artrioventrikularklappe des herzens |
EP2478868A1 (de) | 2011-01-25 | 2012-07-25 | The Provost, Fellows, Foundation Scholars, and the other Members of Board, of the College of the Holy and Undivided Trinity of Queen Elizabeth | Implantationsvorrichtung |
US8845717B2 (en) | 2011-01-28 | 2014-09-30 | Middle Park Medical, Inc. | Coaptation enhancement implant, system, and method |
US8888843B2 (en) | 2011-01-28 | 2014-11-18 | Middle Peak Medical, Inc. | Device, system, and method for transcatheter treatment of valve regurgitation |
US8932343B2 (en) | 2011-02-01 | 2015-01-13 | St. Jude Medical, Cardiology Division, Inc. | Blunt ended stent for prosthetic heart valve |
WO2012106491A1 (en) | 2011-02-02 | 2012-08-09 | St. Jude Medical, Inc. | System and method for loading a collapsile heart valve into a delivery device |
WO2012161769A1 (en) | 2011-02-18 | 2012-11-29 | Guided Delivery Systems Inc. | Implant retrieval device |
US8876686B2 (en) | 2011-02-18 | 2014-11-04 | Vascor, Inc | Control of blood flow assist systems |
US10709449B2 (en) | 2011-02-18 | 2020-07-14 | Ancora Heart, Inc. | Systems and methods for variable stiffness tethers |
US9155619B2 (en) | 2011-02-25 | 2015-10-13 | Edwards Lifesciences Corporation | Prosthetic heart valve delivery apparatus |
WO2012127309A1 (en) | 2011-03-21 | 2012-09-27 | Ontorfano Matteo | Disk-based valve apparatus and method for the treatment of valve dysfunction |
US9072511B2 (en) | 2011-03-25 | 2015-07-07 | Kardium Inc. | Medical kit for constricting tissue or a bodily orifice, for example, a mitral valve |
US9308087B2 (en) | 2011-04-28 | 2016-04-12 | Neovasc Tiara Inc. | Sequentially deployed transcatheter mitral valve prosthesis |
US9554897B2 (en) | 2011-04-28 | 2017-01-31 | Neovasc Tiara Inc. | Methods and apparatus for engaging a valve prosthesis with tissue |
US8747462B2 (en) | 2011-05-17 | 2014-06-10 | Boston Scientific Scimed, Inc. | Corkscrew annuloplasty device |
US20120296349A1 (en) | 2011-05-17 | 2012-11-22 | Boston Scientific Scimed, Inc. | Percutaneous Mitral Annulus Mini-Plication |
WO2012158189A1 (en) | 2011-05-17 | 2012-11-22 | Boston Scientific Scimed, Inc. | Annuloplasty ring with anchors fixed by curing polymer |
US8945209B2 (en) | 2011-05-20 | 2015-02-03 | Edwards Lifesciences Corporation | Encapsulated heart valve |
US9180009B2 (en) | 2011-05-25 | 2015-11-10 | Medtronic, Inc. | Droop tester apparatus and method |
US9289282B2 (en) | 2011-05-31 | 2016-03-22 | Edwards Lifesciences Corporation | System and method for treating valve insufficiency or vessel dilatation |
US9402721B2 (en) | 2011-06-01 | 2016-08-02 | Valcare, Inc. | Percutaneous transcatheter repair of heart valves via trans-apical access |
US10117765B2 (en) | 2011-06-14 | 2018-11-06 | W.L. Gore Associates, Inc | Apposition fiber for use in endoluminal deployment of expandable implants |
US8840664B2 (en) | 2011-06-15 | 2014-09-23 | Edwards Lifesciences Corporation | Heart valve prosthesis anchoring device and methods |
WO2012175483A1 (en) | 2011-06-20 | 2012-12-27 | Jacques Seguin | Prosthetic leaflet assembly for repairing a defective cardiac valve and methods of using the same |
EP3964176A1 (de) | 2011-06-21 | 2022-03-09 | Twelve, Inc. | Herzklappenprothesenvorrichtungen |
ES2664243T3 (es) | 2011-06-23 | 2018-04-18 | Valtech Cardio, Ltd. | Elemento de cierre para su uso con una estructura de anuloplastia |
US8920482B2 (en) | 2011-06-30 | 2014-12-30 | Cook Medical Technologies Llc | Stent delivery system |
EP2731558B1 (de) | 2011-07-12 | 2015-09-09 | Rush University Medical Center | Trägersystem für bifurkationsgefässstent mit gezippten kathetern |
US20130018450A1 (en) | 2011-07-13 | 2013-01-17 | Hunt James B | Prosthesis delivery system with retention sleeve |
CN103997978A (zh) | 2011-07-13 | 2014-08-20 | 通用医疗公司 | 用于带有前十字韧带替代物的膝关节置换的方法和装置 |
US8795357B2 (en) | 2011-07-15 | 2014-08-05 | Edwards Lifesciences Corporation | Perivalvular sealing for transcatheter heart valve |
US9119716B2 (en) | 2011-07-27 | 2015-09-01 | Edwards Lifesciences Corporation | Delivery systems for prosthetic heart valve |
EP3417813B1 (de) | 2011-08-05 | 2020-05-13 | Cardiovalve Ltd | Perkutaner mitralklappenersatz |
US8852272B2 (en) | 2011-08-05 | 2014-10-07 | Mitraltech Ltd. | Techniques for percutaneous mitral valve replacement and sealing |
WO2013021374A2 (en) | 2011-08-05 | 2013-02-14 | Mitraltech Ltd. | Techniques for percutaneous mitral valve replacement and sealing |
US20140324164A1 (en) | 2011-08-05 | 2014-10-30 | Mitraltech Ltd. | Techniques for percutaneous mitral valve replacement and sealing |
US20130041451A1 (en) | 2011-08-09 | 2013-02-14 | Cook Medical Technologies Llc | Prosthesis deployment system for open surgical repair |
WO2013021384A1 (en) | 2011-08-11 | 2013-02-14 | Yeda Research And Development Co. Ltd | Compositions and methods for modulating apoptosis |
EP3403616B1 (de) | 2011-08-11 | 2022-05-11 | Tendyne Holdings, Inc. | Verbesserungen für prothesenklappen und damit zusammenhängende erfindungen |
CN202277398U (zh) * | 2011-08-11 | 2012-06-20 | 北京市普惠生物医学工程有限公司 | 一种新型人工生物心脏瓣膜 |
US20130331929A1 (en) | 2011-09-09 | 2013-12-12 | Endoluminal Sciences Pty Ltd. | Means for Controlled Sealing of Endovascular Devices |
WO2013035864A1 (ja) | 2011-09-09 | 2013-03-14 | 新幹工業株式会社 | 弁付きステント、弁付きステント形成用基材、及び弁付きステントの生産方法 |
US9662206B2 (en) | 2011-09-12 | 2017-05-30 | Highlife Sas | Transcatheter valve prosthesis |
US9387075B2 (en) | 2011-09-12 | 2016-07-12 | Highlife Sas | Transcatheter valve prosthesis |
US9358108B2 (en) | 2011-09-12 | 2016-06-07 | Highlife Sas | Transcatheter valve prosthesis |
US8945177B2 (en) | 2011-09-13 | 2015-02-03 | Abbott Cardiovascular Systems Inc. | Gripper pusher mechanism for tissue apposition systems |
US9011468B2 (en) | 2011-09-13 | 2015-04-21 | Abbott Cardiovascular Systems Inc. | Independent gripper |
US8900295B2 (en) | 2011-09-26 | 2014-12-02 | Edwards Lifesciences Corporation | Prosthetic valve with ventricular tethers |
US9554904B2 (en) | 2011-09-28 | 2017-01-31 | Medtronic CV Luxembourg S.a.r.l. | Distal tip assembly for a heart valve delivery catheter |
CA2854116C (en) | 2011-09-28 | 2019-04-30 | Mitracore Technologies Inc. | Apparatuses and methods for cutting a tissue bridge and/or removing a heart valve clip or suture |
US10624664B2 (en) | 2011-09-28 | 2020-04-21 | Evalve, Inc. | Apparatuses and methods for cutting a tissue bridge and/or removing a heart valve clip or suture |
US8764798B2 (en) | 2011-10-03 | 2014-07-01 | Smith & Nephew, Inc. | Knotless suture anchor |
WO2013059747A1 (en) * | 2011-10-19 | 2013-04-25 | Foundry Newco Xii, Inc. | Prosthetic heart valve devices, prosthetic mitral valves and associated systems and methods |
US9039757B2 (en) | 2011-10-19 | 2015-05-26 | Twelve, Inc. | Prosthetic heart valve devices, prosthetic mitral valves and associated systems and methods |
US9763780B2 (en) | 2011-10-19 | 2017-09-19 | Twelve, Inc. | Devices, systems and methods for heart valve replacement |
US9827093B2 (en) | 2011-10-21 | 2017-11-28 | Edwards Lifesciences Cardiaq Llc | Actively controllable stent, stent graft, heart valve and method of controlling same |
US20130116776A1 (en) | 2011-11-04 | 2013-05-09 | Valtech Cardio, Ltd. | External aortic ring and spool mechanism therefor |
US8858623B2 (en) | 2011-11-04 | 2014-10-14 | Valtech Cardio, Ltd. | Implant having multiple rotational assemblies |
EP3970627B1 (de) | 2011-11-08 | 2023-12-20 | Edwards Lifesciences Innovation (Israel) Ltd. | Gesteuerte lenkfunktionalität für ein implantatabgabewerkzeug |
EP2591754B1 (de) | 2011-11-10 | 2015-02-25 | Medtentia International Ltd Oy | Vorrichtung und Verfahren zur Verbesserung der Funktion einer Herzklappe |
US9782282B2 (en) | 2011-11-14 | 2017-10-10 | W. L. Gore & Associates, Inc. | External steerable fiber for use in endoluminal deployment of expandable devices |
US9877858B2 (en) | 2011-11-14 | 2018-01-30 | W. L. Gore & Associates, Inc. | External steerable fiber for use in endoluminal deployment of expandable devices |
US9387097B2 (en) | 2011-11-16 | 2016-07-12 | W. L. Gore & Associates, Inc. | Implant assembly with tactile indicator |
FR2982763B1 (fr) | 2011-11-17 | 2015-07-17 | Ct Hospitalier Regional Universitaire D Amiens | Implant destine a etre place dans un passage de circulation du sang et dispositif de traitement associe |
US9445893B2 (en) | 2011-11-21 | 2016-09-20 | Mor Research Applications Ltd. | Device for placement in the tricuspid annulus |
EP2785276A4 (de) | 2011-12-01 | 2015-08-12 | Woodstock Man Pty Ltd | Endoluminale prothese |
US9364359B2 (en) | 2011-12-08 | 2016-06-14 | W. L. Gore & Associates, Inc. | Systems and methods for delivery of a medical device |
CA3097364C (en) | 2011-12-09 | 2023-08-01 | Edwards Lifesciences Corporation | Prosthetic heart valve having improved commissure supports |
EP2886084B1 (de) | 2011-12-12 | 2018-02-14 | David Alon | Vorrichtung zur Herzklappenreparatur |
US9827092B2 (en) | 2011-12-16 | 2017-11-28 | Tendyne Holdings, Inc. | Tethers for prosthetic mitral valve |
US9078747B2 (en) | 2011-12-21 | 2015-07-14 | Edwards Lifesciences Corporation | Anchoring device for replacing or repairing a heart valve |
WO2013096541A1 (en) | 2011-12-21 | 2013-06-27 | The Trustees Of The University Of Pennsylvania | Platforms for mitral valve replacement |
FR2985659B1 (fr) | 2012-01-13 | 2015-03-06 | Assist Publ Hopitaux De Paris | Dispositif d'ancrage d'une valve cardiaque prothetique. |
KR101198775B1 (ko) | 2012-01-18 | 2012-11-12 | 박광태 | 수술용 도구, 이를 위한 수술용 메쉬와 수술용 견인수단, 이를 이용한 수술 방법 |
EP2620125B1 (de) | 2012-01-24 | 2017-10-11 | Medtentia International Ltd Oy | Anordnung, schleifenförmige Stütze, Herzklappenprothese und Verfahren zum Reparieren oder Ersetzen einer natürlichen Herzklappe |
US8961602B2 (en) | 2012-01-27 | 2015-02-24 | St. Jude Medical, Cardiology Division, Inc. | Adjustment suture markers for adjustable annuloplasty ring |
EP3326585B1 (de) | 2012-01-31 | 2019-06-19 | Mitral Valve Technologies Sàrl | Mitralklappenanschlussvorrichtungen und -systeme |
US9687371B2 (en) | 2012-02-14 | 2017-06-27 | W. L. Gore & Associates, Inc. | Endoprosthesis having aligned legs for ease of cannulation |
EP2818139A4 (de) | 2012-02-24 | 2015-10-21 | Terumo Corp | Vorrichtung für die freisetzung einer stentprothese |
EP2819618B1 (de) | 2012-02-28 | 2018-05-02 | Mvalve Technologies Ltd. | Monozyklischer herzklappenträger |
US20150094802A1 (en) | 2012-02-28 | 2015-04-02 | Mvalve Technologies Ltd. | Single-ring cardiac valve support |
US20130304197A1 (en) | 2012-02-28 | 2013-11-14 | Mvalve Technologies Ltd. | Cardiac valve modification device |
EP3542758B1 (de) | 2012-02-29 | 2022-12-14 | Valcare, Inc. | Perkutane annuloplastiesystem mit anterior-posterior-einstellung |
US9180008B2 (en) | 2012-02-29 | 2015-11-10 | Valcare, Inc. | Methods, devices, and systems for percutaneously anchoring annuloplasty rings |
US9375308B2 (en) | 2012-03-13 | 2016-06-28 | W. L. Gore & Associates, Inc. | External steerable fiber for use in endoluminal deployment of expandable devices |
ES2535295T3 (es) | 2012-03-23 | 2015-05-08 | Sorin Group Italia S.R.L. | Prótesis de válvula plegable |
US9066800B2 (en) | 2012-03-28 | 2015-06-30 | Medtronic, Inc. | Dual valve prosthesis for transcatheter valve implantation |
US8926694B2 (en) | 2012-03-28 | 2015-01-06 | Medtronic Vascular Galway Limited | Dual valve prosthesis for transcatheter valve implantation |
US9011515B2 (en) | 2012-04-19 | 2015-04-21 | Caisson Interventional, LLC | Heart valve assembly systems and methods |
US9427315B2 (en) | 2012-04-19 | 2016-08-30 | Caisson Interventional, LLC | Valve replacement systems and methods |
US9314325B2 (en) | 2012-04-27 | 2016-04-19 | Cook Medical Technologies Llc | Anti-aspiration prosthesis |
US9427303B2 (en) | 2012-04-27 | 2016-08-30 | Cook Medical Technologies Llc | Anti-aspiration valve |
US9277990B2 (en) | 2012-05-04 | 2016-03-08 | St. Jude Medical, Cardiology Division, Inc. | Hypotube shaft with articulation mechanism |
CA2874208C (en) | 2012-05-20 | 2020-05-12 | Mitralheal Ltd. | Prosthetic mitral valve |
CN102652694B (zh) * | 2012-05-24 | 2014-06-25 | 上海欣吉特生物科技有限公司 | 人工心脏瓣膜 |
US9345573B2 (en) | 2012-05-30 | 2016-05-24 | Neovasc Tiara Inc. | Methods and apparatus for loading a prosthesis onto a delivery system |
DE102012010798A1 (de) | 2012-06-01 | 2013-12-05 | Universität Duisburg-Essen | Implantierbare Vorrichtung zur Verbesserung oder Behebung einer Herzklappeninsuffizienz |
US9241791B2 (en) | 2012-06-29 | 2016-01-26 | St. Jude Medical, Cardiology Division, Inc. | Valve assembly for crimp profile |
WO2014011888A1 (en) | 2012-07-12 | 2014-01-16 | Boston Scientific Scimed, Inc. | Low profile heart valve delivery system and method |
WO2014022124A1 (en) | 2012-07-28 | 2014-02-06 | Tendyne Holdings, Inc. | Improved multi-component designs for heart valve retrieval device, sealing structures and stent assembly |
WO2014021905A1 (en) | 2012-07-30 | 2014-02-06 | Tendyne Holdings, Inc. | Improved delivery systems and methods for transcatheter prosthetic valves |
US9486349B2 (en) | 2012-08-10 | 2016-11-08 | W. L. Gore & Associates, Inc. | Systems and methods of deployment of endoluminal devices |
US9232995B2 (en) | 2013-01-08 | 2016-01-12 | Medtronic, Inc. | Valve prosthesis and method for delivery |
US10206775B2 (en) | 2012-08-13 | 2019-02-19 | Medtronic, Inc. | Heart valve prosthesis |
US9717595B2 (en) | 2012-09-05 | 2017-08-01 | Medtronic Vascular Galway | Trans-aortic delivery system with containment capsule centering device |
US9510946B2 (en) | 2012-09-06 | 2016-12-06 | Edwards Lifesciences Corporation | Heart valve sealing devices |
WO2014049106A1 (en) | 2012-09-27 | 2014-04-03 | Symetis Sa | Stent-valve, delivery apparatus, and stent-holder therefor |
CA2885354A1 (en) | 2012-09-29 | 2014-04-03 | Mitralign, Inc. | Plication lock delivery system and method of use thereof |
US20140099726A1 (en) | 2012-10-10 | 2014-04-10 | Two Pore Guys, Inc. | Device for characterizing polymers |
US20140106951A1 (en) | 2012-10-15 | 2014-04-17 | W. L. Gore & Associates, Inc. | Methods and systems for securing a sleeve for endoluminal devices |
EP3730066A1 (de) | 2012-10-23 | 2020-10-28 | Valtech Cardio, Ltd. | Perkutane gewebeankertechniken |
EP2911594B1 (de) | 2012-10-23 | 2018-12-05 | Valtech Cardio, Ltd. | Gesteuerte lenkfunktionalität für ein implantateinführungswerkzeug |
US9763817B2 (en) | 2012-10-29 | 2017-09-19 | Cook Medical Technologies Llc | Delivery system with curved preloaded catheter |
US10010654B2 (en) | 2012-10-30 | 2018-07-03 | W. L. Gore & Associates, Inc. | Sleeve for medical device assembly |
US9023099B2 (en) | 2012-10-31 | 2015-05-05 | Medtronic Vascular Galway Limited | Prosthetic mitral valve and delivery method |
US9387105B2 (en) | 2012-11-12 | 2016-07-12 | W.L. Gore & Associates, Inc | Sleeves for expandable medical devices and methods of making the same |
US9610183B2 (en) | 2012-11-12 | 2017-04-04 | W.L. Gore & Associates, Inc. | Friction fiber sleeve retraction system |
US8628571B1 (en) | 2012-11-13 | 2014-01-14 | Mitraltech Ltd. | Percutaneously-deliverable mechanical valve |
US20140142688A1 (en) | 2012-11-20 | 2014-05-22 | Medtronic CV Luxembourg S.a.r.l. | Medical Device Delivery System and Methods of Delivering a Medical Device |
US9730793B2 (en) | 2012-12-06 | 2017-08-15 | Valtech Cardio, Ltd. | Techniques for guide-wire based advancement of a tool |
EP2745812B1 (de) | 2012-12-19 | 2017-01-18 | Cook Medical Technologies LLC | Repositionierbare durchmesserbeschränkungen |
US9101469B2 (en) | 2012-12-19 | 2015-08-11 | W. L. Gore & Associates, Inc. | Prosthetic heart valve with leaflet shelving |
US10321986B2 (en) | 2012-12-19 | 2019-06-18 | W. L. Gore & Associates, Inc. | Multi-frame prosthetic heart valve |
CN103908729B (zh) | 2012-12-28 | 2016-12-28 | 米特拉利根公司 | 能量辅助组织穿刺装置及其使用方法 |
US9364322B2 (en) | 2012-12-31 | 2016-06-14 | Edwards Lifesciences Corporation | Post-implant expandable surgical heart valve configurations |
US9066801B2 (en) | 2013-01-08 | 2015-06-30 | Medtronic, Inc. | Valve prosthesis and method for delivery |
US9132007B2 (en) | 2013-01-10 | 2015-09-15 | Medtronic CV Luxembourg S.a.r.l. | Anti-paravalvular leakage components for a transcatheter valve prosthesis |
ES2934670T3 (es) | 2013-01-24 | 2023-02-23 | Cardiovalve Ltd | Válvulas protésicas ancladas de forma ventricular |
GB2510151B (en) | 2013-01-25 | 2015-07-22 | Cook Medical Technologies Llc | Vascular plug |
CN109938878B (zh) | 2013-02-04 | 2021-08-31 | 托尔福公司 | 用于人工心脏瓣膜装置的液压输送系统及相关方法 |
US9439763B2 (en) | 2013-02-04 | 2016-09-13 | Edwards Lifesciences Corporation | Prosthetic valve for replacing mitral valve |
US9456897B2 (en) | 2013-02-21 | 2016-10-04 | Medtronic, Inc. | Transcatheter valve prosthesis and a concurrently delivered sealing component |
US9724084B2 (en) | 2013-02-26 | 2017-08-08 | Mitralign, Inc. | Devices and methods for percutaneous tricuspid valve repair |
JP6473089B2 (ja) | 2013-03-05 | 2019-02-20 | メリット・メディカル・システムズ・インコーポレイテッドMerit Medical Systems,Inc. | 補強弁 |
US10583002B2 (en) | 2013-03-11 | 2020-03-10 | Neovasc Tiara Inc. | Prosthetic valve with anti-pivoting mechanism |
US8986375B2 (en) | 2013-03-12 | 2015-03-24 | Medtronic, Inc. | Anti-paravalvular leakage component for a transcatheter valve prosthesis |
WO2014164364A1 (en) | 2013-03-13 | 2014-10-09 | Aortic Innovations, Llc | Dual frame stent and valve devices and implantation |
US20140277358A1 (en) | 2013-03-13 | 2014-09-18 | DePuy Synthes Products, LLC | Striped stent introducer |
US20140277427A1 (en) | 2013-03-14 | 2014-09-18 | Cardiaq Valve Technologies, Inc. | Prosthesis for atraumatically grasping intralumenal tissue and methods of delivery |
US9681951B2 (en) | 2013-03-14 | 2017-06-20 | Edwards Lifesciences Cardiaq Llc | Prosthesis with outer skirt and anchors |
US9226839B1 (en) | 2013-03-14 | 2016-01-05 | W. L. Gore & Associates, Inc. | Torque sleeve |
US9011526B2 (en) | 2013-03-14 | 2015-04-21 | Cormatrix Cardiovascular, Inc | Tubular extracellular matrix prosthetic valve |
US10449333B2 (en) | 2013-03-14 | 2019-10-22 | Valtech Cardio, Ltd. | Guidewire feeder |
US9232994B2 (en) * | 2013-03-15 | 2016-01-12 | Medtronic Vascular Galway Limited | Stented prosthetic heart valve and methods for making |
EP2968847B1 (de) | 2013-03-15 | 2023-03-08 | Edwards Lifesciences Corporation | Translationskatheter systeme |
EP4183373A1 (de) | 2013-03-15 | 2023-05-24 | Twelve, Inc. | Herzklappenprothesenvorrichtungen, mitralklappenprothesen sowie zugehörige systeme |
KR102423195B1 (ko) | 2013-03-15 | 2022-07-20 | 네비게이트 카디악 스트럭쳐스, 인크. | 카테터 안내된 치환 판막 장치 및 방법 |
US20140296969A1 (en) | 2013-04-02 | 2014-10-02 | Tendyne Holdlings, Inc. | Anterior Leaflet Clip Device for Prosthetic Mitral Valve |
FR3004638B1 (fr) | 2013-04-19 | 2015-05-29 | Invalv Lab | Implant, notamment destine a etre place dans une valve auriculo-ventriculaire cardiaque, comportant un systeme d'ecartement des bras proximaux |
DE102013208038B4 (de) | 2013-05-02 | 2016-09-08 | Michael Siegenthaler | Katheterbasierendes Herzunterstützungssystem |
KR102245192B1 (ko) | 2013-05-06 | 2021-04-29 | 온테라 인크. | 나노포어를 이용한 표적 검출 |
EP2994751B1 (de) | 2013-05-06 | 2018-10-10 | Two Pore Guys, Inc. | Bestimmungsverfahren für biologische zielkomplexe mittles eine nanopore und eines fusionsproteins bindemittel |
US10188515B2 (en) | 2013-05-13 | 2019-01-29 | Medtronic Vascular Inc. | Devices and methods for crimping a medical device |
CA2908342C (en) | 2013-05-20 | 2021-11-30 | Edwards Lifesciences Corporation | Prosthetic heart valve delivery apparatus |
JP2016523606A (ja) | 2013-05-29 | 2016-08-12 | ムバルブ・テクノロジーズ・リミテッド | 弁葉を取り付けた心臓弁支持装置 |
US9610159B2 (en) | 2013-05-30 | 2017-04-04 | Tendyne Holdings, Inc. | Structural members for prosthetic mitral valves |
US20140358224A1 (en) | 2013-05-30 | 2014-12-04 | Tendyne Holdlings, Inc. | Six cell inner stent device for prosthetic mitral valves |
CN106618802B (zh) | 2013-06-06 | 2018-02-06 | 戴维·阿隆 | 心脏瓣膜修复和更换 |
US9788983B2 (en) | 2013-06-21 | 2017-10-17 | Abbott Cardiovascular Systems Inc. | Removable sheath assembly for a polymer scaffold |
WO2014210219A1 (en) | 2013-06-25 | 2014-12-31 | Two Pore Guys, Inc. | Multiplexed biomarker quantitation by nanopore analysis of biomarker-polymer complexes |
WO2014210108A1 (en) | 2013-06-25 | 2014-12-31 | Mitralign, Inc. | Percutaneous valve repair by reshaping and resizing right ventricle |
US20140379076A1 (en) | 2013-06-25 | 2014-12-25 | Tendyne Holdings, Inc. | Halo Wire Fluid Seal Device for Prosthetic Mitral Valves |
US10028832B2 (en) | 2013-07-10 | 2018-07-24 | Medtronic, Inc. | Helical coil mitral valve annuloplasty systems and methods |
US10524904B2 (en) | 2013-07-11 | 2020-01-07 | Medtronic, Inc. | Valve positioning device |
US9561103B2 (en) | 2013-07-17 | 2017-02-07 | Cephea Valve Technologies, Inc. | System and method for cardiac valve repair and replacement |
EP3039155B1 (de) | 2013-08-26 | 2019-10-09 | Ontera Inc. | Molekülnachweis mithilfe von boronsäuresubstituierten sonden |
USD730520S1 (en) | 2013-09-04 | 2015-05-26 | St. Jude Medical, Cardiology Division, Inc. | Stent with commissure attachments |
USD730521S1 (en) | 2013-09-04 | 2015-05-26 | St. Jude Medical, Cardiology Division, Inc. | Stent with commissure attachments |
US9393111B2 (en) * | 2014-01-15 | 2016-07-19 | Sino Medical Sciences Technology Inc. | Device and method for mitral valve regurgitation treatment |
WO2015059699A2 (en) | 2013-10-23 | 2015-04-30 | Valtech Cardio, Ltd. | Anchor magazine |
US9421094B2 (en) | 2013-10-23 | 2016-08-23 | Caisson Interventional, LLC | Methods and systems for heart valve therapy |
WO2015079443A1 (en) | 2013-11-28 | 2015-06-04 | Mvalve Technologies Ltd. | Intracardiac devices comprising stabilizing elements having improved fatigue resistance |
US9610162B2 (en) | 2013-12-26 | 2017-04-04 | Valtech Cardio, Ltd. | Implantation of flexible implant |
US9980832B2 (en) | 2014-01-28 | 2018-05-29 | Sanford Health | Pararenal and thoracic arch stent graft and methods for use |
WO2015120122A2 (en) | 2014-02-05 | 2015-08-13 | Robert Vidlund | Apparatus and methods for transfemoral delivery of prosthetic mitral valve |
US9072604B1 (en) | 2014-02-11 | 2015-07-07 | Gilberto Melnick | Modular transcatheter heart valve and implantation method |
CN109674560B (zh) | 2014-02-21 | 2022-04-01 | 米特拉尔维尔福科技有限责任公司 | 用于递送人工二尖瓣和锚固装置的装置、系统和方法 |
USD755384S1 (en) | 2014-03-05 | 2016-05-03 | Edwards Lifesciences Cardiaq Llc | Stent |
EP3116409B1 (de) | 2014-03-10 | 2023-07-26 | Tendyne Holdings, Inc. | Vorrichtungen zur positionierung und überwachung der gurtbelastung für eine künstliche mitralklappe |
WO2015152980A1 (en) | 2014-03-31 | 2015-10-08 | St. Jude Medical, Cardiology Division, Inc. | Paravalvular sealing via extended cuff mechanisms |
US10149758B2 (en) | 2014-04-01 | 2018-12-11 | Medtronic, Inc. | System and method of stepped deployment of prosthetic heart valve |
US9833346B2 (en) | 2014-04-04 | 2017-12-05 | W. L. Gore & Associates, Inc. | Deployment handle for a medical device deployment system |
WO2015169866A1 (en) | 2014-05-06 | 2015-11-12 | Dsm Ip Assets B.V. | Prosthetic valve and method of making a prosthetic valve |
US10195025B2 (en) * | 2014-05-12 | 2019-02-05 | Edwards Lifesciences Corporation | Prosthetic heart valve |
EP3143165A4 (de) | 2014-05-15 | 2018-05-16 | Two Pore Guys, Inc. | Gerüstdatenspeicherung und zielerfassung in einer probe mit einer nanopore |
EP3142608B1 (de) | 2014-05-16 | 2024-05-15 | TruLeaf Medical Ltd. | Herzklappenersatz |
CN106456328A (zh) | 2014-05-19 | 2017-02-22 | 爱德华兹生命科学卡迪尔克有限责任公司 | 带有环形活瓣的二尖瓣膜替代品 |
EP3134033B1 (de) | 2014-05-29 | 2018-04-04 | Edwards Lifesciences CardiAQ LLC | Prothese und einführungsvorrichtung |
US9532870B2 (en) | 2014-06-06 | 2017-01-03 | Edwards Lifesciences Corporation | Prosthetic valve for replacing a mitral valve |
US9662203B2 (en) | 2014-06-11 | 2017-05-30 | Medtronic Vascular, Inc. | Prosthetic valve with vortice-inducing baffle |
US9974647B2 (en) | 2014-06-12 | 2018-05-22 | Caisson Interventional, LLC | Two stage anchor and mitral valve assembly |
US9180005B1 (en) | 2014-07-17 | 2015-11-10 | Millipede, Inc. | Adjustable endolumenal mitral valve ring |
WO2016016899A1 (en) | 2014-07-30 | 2016-02-04 | Mitraltech Ltd. | Articulatable prosthetic valve |
CN106659567B (zh) | 2014-08-18 | 2019-06-14 | W.L.戈尔及同仁股份有限公司 | 带有用于假体瓣膜的一体缝合封套的框架 |
CA2962234A1 (en) | 2014-09-26 | 2016-03-31 | Two Pore Guys, Inc. | Target sequence detection by nanopore sensing of synthetic probes |
US10507101B2 (en) | 2014-10-13 | 2019-12-17 | W. L. Gore & Associates, Inc. | Valved conduit |
US9750605B2 (en) | 2014-10-23 | 2017-09-05 | Caisson Interventional, LLC | Systems and methods for heart valve therapy |
US9750607B2 (en) | 2014-10-23 | 2017-09-05 | Caisson Interventional, LLC | Systems and methods for heart valve therapy |
CN115721454A (zh) | 2014-12-04 | 2023-03-03 | 爱德华兹生命科学公司 | 用于修复心脏瓣膜的经皮夹具 |
US9439757B2 (en) | 2014-12-09 | 2016-09-13 | Cephea Valve Technologies, Inc. | Replacement cardiac valves and methods of use and manufacture |
WO2016096930A1 (en) | 2014-12-15 | 2016-06-23 | Vivasure Medical Limited | Implantable sealable member with mesh layer |
US9937037B2 (en) | 2014-12-18 | 2018-04-10 | W. L. Gore & Associates, Inc. | Prosthetic valved conduits with mechanically coupled leaflets |
AU2016215453A1 (en) | 2015-02-02 | 2017-08-10 | Two Pore Guys, Inc. | Nanopore detection of target polynucleotides from sample background |
AU2016215455A1 (en) | 2015-02-02 | 2017-08-17 | Ontera Inc. | Labile linkers for biomarker detection |
US20160220367A1 (en) | 2015-02-04 | 2016-08-04 | Medtronic Vascular, Inc. | Balloon valvuloplasty delivery system |
US9974651B2 (en) | 2015-02-05 | 2018-05-22 | Mitral Tech Ltd. | Prosthetic valve with axially-sliding frames |
WO2016125160A1 (en) | 2015-02-05 | 2016-08-11 | Mitraltech Ltd. | Prosthetic valve with axially-sliding frames |
US10039637B2 (en) | 2015-02-11 | 2018-08-07 | Edwards Lifesciences Corporation | Heart valve docking devices and implanting methods |
JP6763885B2 (ja) | 2015-02-20 | 2020-09-30 | 4シー メディカル テクノロジーズ,インコーポレイテッド | 心臓処置用の装置、システムおよび方法 |
US9983191B2 (en) | 2015-03-11 | 2018-05-29 | Two Pore Guys, Inc. | Nanopore detection of small molecules through competition assays |
EP3270827B1 (de) | 2015-03-19 | 2023-12-20 | Caisson Interventional, LLC | Systeme für herzklappentherapie |
US20180116843A1 (en) | 2015-03-20 | 2018-05-03 | Jenavalve Technology, Inc. | Heart valve prosthesis delivery system and method for delivery of heart valve prosthesis with introducer sheath |
WO2016154168A1 (en) | 2015-03-23 | 2016-09-29 | St. Jude Medical, Cardiology Division, Inc. | Heart valve repair |
US10441416B2 (en) | 2015-04-21 | 2019-10-15 | Edwards Lifesciences Corporation | Percutaneous mitral valve replacement device |
US10232564B2 (en) | 2015-04-29 | 2019-03-19 | Edwards Lifesciences Corporation | Laminated sealing member for prosthetic heart valve |
US10376363B2 (en) | 2015-04-30 | 2019-08-13 | Edwards Lifesciences Cardiaq Llc | Replacement mitral valve, delivery system for replacement mitral valve and methods of use |
AU2016262564B2 (en) | 2015-05-14 | 2020-11-05 | Cephea Valve Technologies, Inc. | Replacement mitral valves |
US20160338706A1 (en) | 2015-05-20 | 2016-11-24 | Edwards Lifesciences Corporation | Atrial septal closure device for re-access |
US10226335B2 (en) | 2015-06-22 | 2019-03-12 | Edwards Lifesciences Cardiaq Llc | Actively controllable heart valve implant and method of controlling same |
US10092400B2 (en) | 2015-06-23 | 2018-10-09 | Edwards Lifesciences Cardiaq Llc | Systems and methods for anchoring and sealing a prosthetic heart valve |
ITUB20152409A1 (it) | 2015-07-22 | 2017-01-22 | Sorin Group Italia Srl | Manicotto valvolare per protesi valvolari e corrispondente dispositivo |
CN205181539U (zh) * | 2015-08-06 | 2016-04-27 | 深圳市第二人民医院 | 一种新型人工生物心脏瓣膜 |
WO2017030940A1 (en) | 2015-08-14 | 2017-02-23 | Caisson Interventional Llc | Systems and methods for heart valve therapy |
US11357499B2 (en) | 2015-08-18 | 2022-06-14 | Lsi Solutions, Inc. | Apparatus for mitral valve repair and methods thereof |
US10117744B2 (en) | 2015-08-26 | 2018-11-06 | Edwards Lifesciences Cardiaq Llc | Replacement heart valves and methods of delivery |
US10350066B2 (en) | 2015-08-28 | 2019-07-16 | Edwards Lifesciences Cardiaq Llc | Steerable delivery system for replacement mitral valve and methods of use |
US10322020B2 (en) | 2015-09-18 | 2019-06-18 | Terumo Corporation | Pushable implant delivery system |
US10456243B2 (en) | 2015-10-09 | 2019-10-29 | Medtronic Vascular, Inc. | Heart valves prostheses and methods for percutaneous heart valve replacement |
EP3337425A4 (de) | 2015-10-13 | 2018-11-07 | Venarum Medical, LLC | Implantierbares ventil und verfahren |
US10327929B2 (en) | 2015-10-30 | 2019-06-25 | Ram Medical Innovations, Llc | Apparatus and method for stabilization of procedural catheter in tortuous vessels |
US10376364B2 (en) | 2015-11-10 | 2019-08-13 | Edwards Lifesciences Corporation | Implant delivery capsule |
CN111329541B (zh) | 2015-11-17 | 2023-09-19 | 波士顿科学国际有限公司 | 用于使心脏瓣环重新定形的可植入装置和输送系统 |
CA3006010C (en) | 2015-12-28 | 2023-09-26 | Tendyne Holdings, Inc. | Atrial pocket closures for prosthetic heart valves |
US10321992B2 (en) | 2016-02-01 | 2019-06-18 | Medtronic, Inc. | Heart valve prostheses having multiple support arms and methods for percutaneous heart valve replacement |
US10265059B2 (en) | 2016-02-04 | 2019-04-23 | Edwards Lifesciences Corporation | Trans-septal closure and port device |
US10531866B2 (en) | 2016-02-16 | 2020-01-14 | Cardiovalve Ltd. | Techniques for providing a replacement valve and transseptal communication |
EP3451973A4 (de) | 2016-05-06 | 2019-12-25 | Transmural Systems LLC | Annuloplastikeingriffe, zugehörige vorrichtungen und verfahren |
WO2017201196A1 (en) | 2016-05-17 | 2017-11-23 | Boston Scientific Scimed, Inc. | Replacement heart valve implant with inflow stitching |
US10716691B2 (en) | 2016-06-24 | 2020-07-21 | Edwards Lifesciences Corporation | Compact crimping device |
US10350062B2 (en) | 2016-07-21 | 2019-07-16 | Edwards Lifesciences Corporation | Replacement heart valve prosthesis |
WO2018025260A1 (en) | 2016-07-31 | 2018-02-08 | Mvalve Technologies Ltd. | Intracardiac devices comprising wire-supported valve leaflets |
GB201613219D0 (en) | 2016-08-01 | 2016-09-14 | Mitraltech Ltd | Minimally-invasive delivery systems |
USD800908S1 (en) | 2016-08-10 | 2017-10-24 | Mitraltech Ltd. | Prosthetic valve element |
WO2018029680A1 (en) | 2016-08-10 | 2018-02-15 | Mitraltech Ltd. | Prosthetic valve with concentric frames |
EP3500214A4 (de) | 2016-08-19 | 2019-07-24 | Edwards Lifesciences Corporation | Lenkbares abgabesystem für ersatzmitralklappe und verfahren zur verwendung |
CR20190069A (es) | 2016-08-26 | 2019-05-14 | Edwards Lifesciences Corp | Valvulas y sistemas de acoplamiento de valvulas corazon |
US10722359B2 (en) | 2016-08-26 | 2020-07-28 | Edwards Lifesciences Corporation | Heart valve docking devices and systems |
CN109843219B (zh) | 2016-08-26 | 2022-04-05 | 爱德华兹生命科学公司 | 多部分置换心脏瓣膜假体 |
US10758348B2 (en) | 2016-11-02 | 2020-09-01 | Edwards Lifesciences Corporation | Supra and sub-annular mitral valve delivery system |
FR3058632B1 (fr) | 2016-11-14 | 2019-01-25 | Laboratoires Invalv | Dispositif de traitement d'une valve biologique avec organe de poussee de la valve |
US10603165B2 (en) | 2016-12-06 | 2020-03-31 | Edwards Lifesciences Corporation | Mechanically expanding heart valve and delivery apparatus therefor |
US10779837B2 (en) | 2016-12-08 | 2020-09-22 | Evalve, Inc. | Adjustable arm device for grasping tissues |
WO2018112429A1 (en) | 2016-12-16 | 2018-06-21 | Edwards Lifesciences Corporation | Deployment systems, tools, and methods for delivering an anchoring device for a prosthetic valve |
CA3047396A1 (en) | 2016-12-20 | 2018-06-28 | Edwards Lifesciences Corporation | Systems and mechanisms for deploying a docking device for a replacement heart valve |
US10905554B2 (en) | 2017-01-05 | 2021-02-02 | Edwards Lifesciences Corporation | Heart valve coaptation device |
WO2018131043A1 (en) | 2017-01-11 | 2018-07-19 | Mitrassist Medical Ltd. | Multi-level cardiac implant |
JP7046078B2 (ja) | 2017-01-23 | 2022-04-01 | セフィア・バルブ・テクノロジーズ,インコーポレイテッド | 置換僧帽弁 |
AU2018203053B2 (en) | 2017-01-23 | 2020-03-05 | Cephea Valve Technologies, Inc. | Replacement mitral valves |
US10675017B2 (en) | 2017-02-07 | 2020-06-09 | Edwards Lifesciences Corporation | Transcatheter heart valve leaflet plication |
JP6788746B2 (ja) | 2017-02-10 | 2020-11-25 | ボストン サイエンティフィック サイムド,インコーポレイテッドBoston Scientific Scimed,Inc. | 心臓弁輪を再形成するための埋め込み可能な機器および送達システム |
US10952852B2 (en) | 2017-02-24 | 2021-03-23 | Abbott Cardiovascular Systems Inc. | Double basket assembly for valve repair |
WO2018165064A1 (en) | 2017-03-06 | 2018-09-13 | Boston Scientific Scimed, Inc. | Replacement heart valve system having docking station with sacrificial valve |
US11224511B2 (en) | 2017-04-18 | 2022-01-18 | Edwards Lifesciences Corporation | Heart valve sealing devices and delivery devices therefor |
BR112019021267A2 (pt) | 2017-04-18 | 2020-05-19 | Edwards Lifesciences Corp | dispositivos de vedação de válvula cardíaca e dispositivos de liberação dos mesmos |
US10327895B2 (en) | 2017-05-05 | 2019-06-25 | Vdyne, Llc | Pressure differential actuated prosthetic medical device |
US10959846B2 (en) | 2017-05-10 | 2021-03-30 | Edwards Lifesciences Corporation | Mitral valve spacer device |
WO2018209313A1 (en) | 2017-05-12 | 2018-11-15 | Evalve, Inc. | Long arm valve repair clip |
US20210401571A9 (en) | 2017-05-31 | 2021-12-30 | Edwards Lifesciences Corporation | Sealing member for prosthetic heart valve |
US11026785B2 (en) | 2017-06-05 | 2021-06-08 | Edwards Lifesciences Corporation | Mechanically expandable heart valve |
US10709591B2 (en) | 2017-06-06 | 2020-07-14 | Twelve, Inc. | Crimping device and method for loading stents and prosthetic heart valves |
EP3634311A1 (de) | 2017-06-08 | 2020-04-15 | Boston Scientific Scimed, Inc. | Herzklappenimplantat mit stützstruktur |
US10888421B2 (en) | 2017-09-19 | 2021-01-12 | Cardiovalve Ltd. | Prosthetic heart valve with pouch |
US11246704B2 (en) | 2017-08-03 | 2022-02-15 | Cardiovalve Ltd. | Prosthetic heart valve |
US10537426B2 (en) | 2017-08-03 | 2020-01-21 | Cardiovalve Ltd. | Prosthetic heart valve |
US11793633B2 (en) | 2017-08-03 | 2023-10-24 | Cardiovalve Ltd. | Prosthetic heart valve |
EP3661457A1 (de) | 2017-08-03 | 2020-06-10 | Cardiovalve Ltd | Herzklappenprothese |
US10575948B2 (en) | 2017-08-03 | 2020-03-03 | Cardiovalve Ltd. | Prosthetic heart valve |
CN117959037A (zh) | 2017-08-04 | 2024-05-03 | 姆维亚克斯股份有限公司 | 用于重塑心脏瓣膜环的递送系统和方法,包括使用磁性工具 |
EP3668449A1 (de) | 2017-08-16 | 2020-06-24 | Boston Scientific Scimed, Inc. | Kommissuranordnung für herzklappenersatz |
CN111031966A (zh) | 2017-08-24 | 2020-04-17 | 美敦力瓦斯科尔勒公司 | 具有偏转部段的经中隔递送系统及使用方法 |
US11051940B2 (en) | 2017-09-07 | 2021-07-06 | Edwards Lifesciences Corporation | Prosthetic spacer device for heart valve |
US10881511B2 (en) | 2017-09-19 | 2021-01-05 | Cardiovalve Ltd. | Prosthetic valve with tissue anchors configured to exert opposing clamping forces on native valve tissue |
US10856982B2 (en) | 2017-09-19 | 2020-12-08 | St. Jude Medical, Cardiology Division, Inc. | Transapical mitral valve delivery system |
US9895226B1 (en) | 2017-10-19 | 2018-02-20 | Mitral Tech Ltd. | Techniques for use with prosthetic valve leaflets |
CN111278387B (zh) | 2017-10-23 | 2022-09-20 | 赛姆斯股份公司 | 人工瓣膜小叶 |
US20190175339A1 (en) | 2017-12-12 | 2019-06-13 | Vdyne, Llc | Septomarginal trabecula attachment for heart valve repair |
GB201720803D0 (en) | 2017-12-13 | 2018-01-24 | Mitraltech Ltd | Prosthetic Valve and delivery tool therefor |
US20190183639A1 (en) | 2017-12-19 | 2019-06-20 | St. Jude Medical, Cardiology Division, Inc. | Transcatheter Mitral Valve: Off-Center Valve Design |
US10231837B1 (en) | 2018-01-09 | 2019-03-19 | Edwards Lifesciences Corporation | Native valve repair devices and procedures |
US10130475B1 (en) | 2018-01-09 | 2018-11-20 | Edwards Lifesciences Corporation | Native valve repair devices and procedures |
US10105222B1 (en) | 2018-01-09 | 2018-10-23 | Edwards Lifesciences Corporation | Native valve repair devices and procedures |
US10136993B1 (en) | 2018-01-09 | 2018-11-27 | Edwards Lifesciences Corporation | Native valve repair devices and procedures |
US10159570B1 (en) | 2018-01-09 | 2018-12-25 | Edwards Lifesciences Corporation | Native valve repair devices and procedures |
US10123873B1 (en) | 2018-01-09 | 2018-11-13 | Edwards Lifesciences Corporation | Native valve repair devices and procedures |
US10238493B1 (en) | 2018-01-09 | 2019-03-26 | Edwards Lifesciences Corporation | Native valve repair devices and procedures |
EP3964175A1 (de) | 2018-01-09 | 2022-03-09 | Edwards Lifesciences Corporation | Vorrichtungen und verfahren zur reparatur einer nativen klappe |
US10076415B1 (en) | 2018-01-09 | 2018-09-18 | Edwards Lifesciences Corporation | Native valve repair devices and procedures |
US10507109B2 (en) | 2018-01-09 | 2019-12-17 | Edwards Lifesciences Corporation | Native valve repair devices and procedures |
US10245144B1 (en) | 2018-01-09 | 2019-04-02 | Edwards Lifesciences Corporation | Native valve repair devices and procedures |
US10111751B1 (en) | 2018-01-09 | 2018-10-30 | Edwards Lifesciences Corporation | Native valve repair devices and procedures |
GB201800399D0 (en) | 2018-01-10 | 2018-02-21 | Mitraltech Ltd | Temperature-control during crimping of an implant |
US10568740B2 (en) | 2018-01-15 | 2020-02-25 | Vdyne, Llc | Device and method to plicate the tricuspid valve |
WO2019195860A2 (en) | 2018-04-04 | 2019-10-10 | Vdyne, Llc | Devices and methods for anchoring transcatheter heart valve |
US11389297B2 (en) | 2018-04-12 | 2022-07-19 | Edwards Lifesciences Corporation | Mitral valve spacer device |
CA3096002A1 (en) | 2018-04-19 | 2019-10-24 | Cardiovalve Ltd. | Prosthetic heart valve with pouch |
CN112399836A (zh) | 2018-05-15 | 2021-02-23 | 波士顿科学国际有限公司 | 置换心脏瓣膜连合组件 |
US10765511B2 (en) | 2018-06-22 | 2020-09-08 | Vdyne, Inc. | Transcatheter heart valve with plication tissue anchors |
US10779937B2 (en) | 2018-06-22 | 2020-09-22 | Vdyne, Inc. | Transcatheter heart valve with plication window and tissue anchors |
US11083571B2 (en) | 2018-06-27 | 2021-08-10 | Edwards Lifesciences Corporation | Frame for prosthetic heart valve |
US10779946B2 (en) | 2018-09-17 | 2020-09-22 | Cardiovalve Ltd. | Leaflet-testing apparatus |
US10321995B1 (en) | 2018-09-20 | 2019-06-18 | Vdyne, Llc | Orthogonally delivered transcatheter heart valve replacement |
US10945844B2 (en) | 2018-10-10 | 2021-03-16 | Edwards Lifesciences Corporation | Heart valve sealing devices and delivery devices therefor |
CA3120859A1 (en) | 2018-11-29 | 2020-06-04 | Edwards Lifesciences Corporation | Catheterization method and apparatus |
CN113677298A (zh) | 2019-02-06 | 2021-11-19 | Inqb8医疗科技有限责任公司 | 心内左心房以及双支持系统 |
WO2020167677A1 (en) | 2019-02-11 | 2020-08-20 | Edwards Lifesciences Corporation | Heart valve sealing devices and delivery devices therefor |
US11464636B2 (en) | 2019-10-11 | 2022-10-11 | Evalve, Inc. | Repair clip for variable tissue thickness |
WO2021092460A1 (en) | 2019-11-08 | 2021-05-14 | Evalve, Inc. | Medical device delivery system with locking system |
US20230059371A1 (en) | 2020-02-04 | 2023-02-23 | Cardiovalve Ltd. | Support-guided steering of a catheter |
CN113747857A (zh) | 2020-03-17 | 2021-12-03 | 卡迪尔维尔福股份有限公司 | 瓣叶分组系统 |
-
2017
- 2017-08-08 WO PCT/IL2017/050873 patent/WO2018029680A1/en unknown
- 2017-08-08 CN CN202210336863.0A patent/CN114587712A/zh active Pending
- 2017-08-08 EP EP21157988.3A patent/EP3848003A1/de active Pending
- 2017-08-08 CA CA3031187A patent/CA3031187A1/en active Pending
- 2017-08-08 CN CN201780061210.3A patent/CN109789018B/zh active Active
- 2017-08-08 EP EP17752184.6A patent/EP3496664B1/de active Active
- 2017-08-08 US US16/324,339 patent/US10856975B2/en active Active
-
2018
- 2018-01-23 US US15/878,206 patent/US9987132B1/en active Active
- 2018-06-01 US US15/995,597 patent/US10098732B1/en active Active
- 2018-08-07 CN CN202310511640.8A patent/CN116616958A/zh active Pending
- 2018-08-07 EP EP18752635.5A patent/EP3664748A1/de active Pending
- 2018-08-07 CN CN201880064313.XA patent/CN111432752B/zh active Active
- 2018-08-07 WO PCT/IL2018/050869 patent/WO2019030753A1/en unknown
- 2018-08-07 CA CA3071598A patent/CA3071598A1/en active Pending
- 2018-08-07 US US16/637,166 patent/US10779939B2/en active Active
-
2020
- 2020-08-31 US US17/007,975 patent/US11779458B2/en active Active
-
2023
- 2023-07-31 US US18/228,229 patent/US20230372090A1/en active Pending
Also Published As
Publication number | Publication date |
---|---|
US11779458B2 (en) | 2023-10-10 |
CA3071598A1 (en) | 2019-02-14 |
US10779939B2 (en) | 2020-09-22 |
US10856975B2 (en) | 2020-12-08 |
CN109789018B (zh) | 2022-04-26 |
US20180153687A1 (en) | 2018-06-07 |
US20200163760A1 (en) | 2020-05-28 |
EP3848003A1 (de) | 2021-07-14 |
US20200390548A1 (en) | 2020-12-17 |
CN116616958A (zh) | 2023-08-22 |
EP3496664A1 (de) | 2019-06-19 |
CN111432752B (zh) | 2023-05-30 |
WO2018029680A1 (en) | 2018-02-15 |
WO2019030753A1 (en) | 2019-02-14 |
CA3031187A1 (en) | 2018-02-15 |
CN109789018A (zh) | 2019-05-21 |
US20180280136A1 (en) | 2018-10-04 |
CN114587712A (zh) | 2022-06-07 |
EP3496664B1 (de) | 2021-09-29 |
US9987132B1 (en) | 2018-06-05 |
US20190175342A1 (en) | 2019-06-13 |
US10098732B1 (en) | 2018-10-16 |
US20230372090A1 (en) | 2023-11-23 |
CN111432752A (zh) | 2020-07-17 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US11779458B2 (en) | Prosthetic valve with leaflet connectors | |
US20210145578A1 (en) | Techniques for deployment of a prosthetic valve | |
US10357360B2 (en) | Prosthetic valve with aligned inner and outer frames |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
STAA | Information on the status of an ep patent application or granted ep patent |
Free format text: STATUS: UNKNOWN |
|
STAA | Information on the status of an ep patent application or granted ep patent |
Free format text: STATUS: THE INTERNATIONAL PUBLICATION HAS BEEN MADE |
|
PUAI | Public reference made under article 153(3) epc to a published international application that has entered the european phase |
Free format text: ORIGINAL CODE: 0009012 |
|
STAA | Information on the status of an ep patent application or granted ep patent |
Free format text: STATUS: REQUEST FOR EXAMINATION WAS MADE |
|
17P | Request for examination filed |
Effective date: 20200225 |
|
AK | Designated contracting states |
Kind code of ref document: A1 Designated state(s): AL AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO RS SE SI SK SM TR |
|
AX | Request for extension of the european patent |
Extension state: BA ME |
|
RIN1 | Information on inventor provided before grant (corrected) |
Inventor name: IAMBERGER, MENI Inventor name: HARARI, BOAZ Inventor name: BAUM, AVIRAM Inventor name: HARITON, ILIA |
|
DAV | Request for validation of the european patent (deleted) | ||
DAX | Request for extension of the european patent (deleted) |